JP2013519438A - Rotatable cutting configuration for ultrasonic surgical instruments - Google Patents

Abstract

  In a general aspect, it is directed to an ultrasonic surgical instrument that includes a handpiece housing that rotatably supports an ultrasonic transducer assembly therein that can be selectively rotated by a motor housed therein. Various forms of blades and sheath attachment configurations are disclosed, and the blades may be selectively rotatable within a hollow outer sheath. The hollow outer sheath has at least one opening therein through which the blade tip can be exposed to tissue. A vacuum may be applied to the cutting tool, or a vacuum is applied through the outer sheath to draw tissue through an opening in the sheath and contact a portion of the blade.

Description

  The present disclosure relates generally to ultrasonic surgical systems, and more particularly to an ultrasonic system that allows a surgeon to perform tissue cutting and coagulation.

  Over the years, a variety of different types of non-ultrasonic driven cutters and shaving devices have been developed for performing surgical procedures. Some of these devices utilize a rotary cutting instrument and others utilize a reciprocating cutting member. For example, shavers are widely used in arthroscopic surgery. These devices typically consist of a power source, a handpiece and a single use end effector. An end effector generally has an inner and an outer tube. The inner tube rotates with respect to the outer tube and cuts tissue at its sharp edges. The inner tube can continuously rotate or vibrate. In addition, such devices may utilize suction channels that move through the interior of the inner tube. For example, US Pat. No. 4,970,354 (McGurk-Burson, et al) discloses a surgical cutting instrument that is not ultrasonically driven, including a rotary cutter for cutting material in a shearing motion. This utilizes an internal cutting member that is rotatable within the outer tube.

  U.S. Pat. No. 3,776,238 (Peyman et al) describes an ophthalmic device in which tissue is cut by the cutting action caused by the sharp end of the inner tube moving relative to the inner surface of the end of the outer tube. Is disclosed. US Pat. No. 5,226,910 (Kajiyama et al) describes another surgical cutting instrument having an inner member that moves relative to an outer member to cut tissue entering through the opening of the outer member. Disclose.

  US Pat. No. 4,922,902 (Wuchinich et al) discloses a method and apparatus for endoscopic removal of tissue utilizing an ultrasonic aspirator. The device uses an ultrasound probe that breaks down soft tissue and sucks it through a narrow opening. U.S. Pat. No. 4,634,420 (Spinosa et al) discloses an apparatus and method for removing tissue from an animal, comprising an elongate instrument having a needle or probe that vibrates laterally at an ultrasonic frequency. Including. The ultrasonic movement of the needle breaks the tissue into pieces. Tissue fragments can be removed from the treatment area by aspiration through a needle conduit. U.S. Pat. No. 3,805,787 (to Banko) discloses yet another ultrasonic instrument having a shielded probe to narrow the beam of ultrasonic energy emitted from the tip of the probe. To do. In one embodiment, the shielding member extends beyond the free end of the probe and prevents the probe from contacting tissue. U.S. Pat. No. 5,213,569 (provided to Davis) discloses a phacoemulsification needle that focuses ultrasound energy. The focusing surface may be chamfered, curved or faceted. U.S. Patent No. 6,984,220 (assigned to Wuchinich) and U.S. Patent Application Publication No. 2005/0177184 (given to Easley) provide a combination of longitudinal and torsional motion through the use of longitudinal torsional resonators. An ultrasonic tissue dissection system is provided. US Patent Application Publication No. 2006/0030797 (A1) (Zhou et al) discloses an ophthalmic surgical device having an ultrasonic transducer and a drive motor for driving a horn. An adapter is provided between the drive motor and the transducer to provide an ultrasonic energy signal to the transducer.

  The use of ultrasonically driven surgical instruments provides several advantages over traditional mechanically driven saws, drills and other instruments, but due to frictional heat at the bone / tissue interface, And temperature increases in adjacent tissues can still be a major problem. Current arthroscopic surgical tools include punches, reciprocating shavers, and radio frequency (RF) devices. Mechanical devices such as punches and shavers produce minimal tissue damage but may leave rough cutting lines that are undesirable in some cases. RF devices produce smoother cutting lines and can cauterize large amounts of soft tissue, but these tend to cause greater tissue damage than mechanical means. Therefore, an apparatus that can provide a smooth cutting surface while providing higher cutting accuracy while not causing excessive tissue damage is desirable.

  Arthroscopic surgery includes performing surgery in the joint space. In order to perform surgery, the joint is typically filled with pressurized saline for expansion and visualization. An ultrasonic instrument that can be used in such a surgical procedure must withstand fluid pressure without causing leakage. However, conventional ultrasonic instruments typically experience significant forces during use. Current seals of ultrasound devices are generally not robust enough to withstand this environment without leaks.

  It would be desirable to provide an ultrasonic surgical instrument that overcomes some of the shortcomings of current instruments. The ultrasonic surgical instruments described herein overcome many of these inefficiencies.

  It would also be desirable to provide a more robust sealing arrangement for ultrasonic surgical instruments used to cut and coagulate in the aqueous environment of arthroscopic surgery.

  The above discussion is intended only to illustrate some of the disadvantages that existed in the field of the various embodiments of the present invention at that time, and should not be viewed as negating the scope of the claims. .

  In connection with the general aspect, an ultrasonic surgical instrument is provided that can include a housing having an ultrasonic transducer assembly rotatably supported therein and in communication with an ultrasonic electrical signal source. A motor can be supported in the housing. The motor communicates with the motor drive signal source and is coupled to the ultrasonic transducer assembly for applying rotational motion to the ultrasonic transducer assembly. The horn can be coupled to an ultrasonic transducer assembly. The hollow outer sheath has a distal tip coupled to the housing and having at least one cutting edge formed thereon. The blade may be coupled to the horn and have a tissue cutting distal end. The blade may be rotatably supported within the outer sheath such that the tissue cutting distal end is biased into cutting engagement with at least one cutting edge of the distal tip of the hollow outer sheath. Is done.

  In connection with another general aspect, an ultrasonic surgical instrument is provided that can include a housing having an ultrasonic transducer assembly rotatably supported therein that is in communication with an ultrasonic electrical signal source. The motor is supported in the housing and can communicate with a motor drive signal source. A motor may be coupled to the ultrasonic transducer assembly to apply rotational motion to the ultrasonic transducer assembly. The horn can be coupled to an ultrasonic transducer assembly. The hollow outer sheath may have a distal tip coupled to the housing and defining a tip cavity therein. The blade may be coupled to the horn and have a tissue cutting distal end. The blade may be rotatably supported in the outer sheath and have a tissue cutting distal end that is rotatably supported in the tip cavity. A friction reducing material may be supported in the tip cavity.

  In connection with another general aspect, an ultrasonic surgical instrument is provided that can include a housing having an ultrasonic transducer assembly rotatably supported therein that is in communication with an ultrasonic electrical signal source. The motor may be supported within the housing and communicate with a motor drive signal source. A motor may be coupled to the ultrasonic transducer assembly to apply rotational motion to the ultrasonic transducer assembly. The horn can be coupled to an ultrasonic transducer assembly. The hollow outer sheath may have a distal tip coupled to the housing and defining a tip cavity. The blade is coupled to the horn and is rotatably supported in the outer sheath. The blade may have a tissue cutting distal end that is rotatably supported within the tip cavity. The low friction material may be provided on at least a portion of the tissue cutting edge of the blade.

The features of the various non-limiting embodiments are set forth with particularity in the claims. However, various non-limiting embodiments, both in terms of construction and method of operation, along with their other objects and advantages, can best be understood with reference to the following description taken in conjunction with the accompanying drawings.
1 is a schematic view of a non-limiting embodiment of a surgical control system. FIG. 3 is a perspective view of a non-limiting embodiment of a control system enclosure. FIG. 6 is a perspective view of another non-limiting embodiment of a control system enclosure configuration. Figure 2 is a cross-sectional view of a non-limiting embodiment of a handpiece. 1 is a partial cross-sectional view of an ultrasonic surgical handpiece that can be utilized with various non-limiting embodiments. FIG. FIG. 3 is a partial cross-sectional view of a non-limiting nosepiece embodiment. FIG. 3 is a partially exploded view of a non-limiting nosepiece embodiment. 1 is a partial cross-sectional view of a non-limiting embodiment of a surgical instrument handpiece. FIG. FIG. 7 is a perspective view of the non-limiting surgical instrument handpiece embodiment of FIG. FIG. 6 is a partial cross-sectional view of another non-limiting surgical instrument handpiece embodiment. FIG. 6 is a partial cross-sectional view of another non-limiting surgical instrument handpiece embodiment. FIG. 10 is a perspective view of the surgical instrument handpiece embodiment shown in FIG. 9. FIG. 3 is a partially exploded view of a non-limiting coupling assembly embodiment for coupling a motor to a transducer assembly. FIG. 4 is a side view of a thin plate member and drive shaft configuration of a non-limiting coupling assembly embodiment. FIG. 13 is an end view of the non-limiting thin plate member embodiment of FIG. 12. 6 is a non-limiting side view of another non-limiting coupling assembly embodiment of a thin plate member and drive shaft configuration. FIG. FIG. 15 is an end view of the non-limiting thin plate member embodiment of FIG. FIG. 6 is a partial cross-sectional view of another non-limiting surgical instrument handpiece embodiment. FIG. 6 is a partial perspective view of a non-limiting outer sheath and blade embodiment. FIG. 18 is a partial perspective view of the non-limiting blade embodiment shown in FIG. FIG. 19 is a partial bottom perspective view of the blade of FIGS. 17 and 18. FIG. 6 is a side view of a portion of another non-limiting blade embodiment. FIG. 6 is a side view of a portion of another non-limiting blade embodiment. FIG. 6 is a partial perspective view of the distal end of another non-limiting outer sheath and blade configuration. FIG. 6 is a partial perspective view of the distal end of another non-limiting outer sheath and blade configuration. FIG. 24 is a side view of a portion of the non-limiting outer sheath embodiment shown in FIG. FIG. 6 is a side view of a portion of another non-limiting blade embodiment. FIG. 6 is a side view of a portion of another non-limiting blade embodiment. FIG. 26 is a partial perspective view of the non-limiting blade embodiment of FIG. 25 within the distal end of another non-limiting outer sheath embodiment. FIG. 6 is a side view of a portion of another non-limiting blade embodiment. FIG. 28 is a partial perspective view of the non-limiting blade embodiment of FIG. 27 within the distal end of another non-limiting outer sheath embodiment. FIG. 29 is a partial cross-sectional view of the non-limiting blade and outer sheath embodiment of FIG. FIG. 6 is a side view of a portion of another non-limiting blade embodiment. FIG. 31 is a partial perspective view of the non-limiting blade embodiment of FIG. 30 within the distal end of another non-limiting outer sheath embodiment. FIG. 32 illustrates the first rotatable position of the non-limiting blade embodiment of FIGS. 30 and 31 within the outer sheath embodiment of FIG. FIG. 32 illustrates a second rotatable position of the non-limiting blade embodiment of FIGS. 30 and 31 within the outer sheath embodiment of FIG. FIG. 32 illustrates a third rotatable position of the blade embodiment of FIGS. 30 and 31 within the outer sheath embodiment of FIG. FIG. 32 illustrates a fourth rotatable position of the blade embodiment of FIGS. 30 and 31 within the outer sheath embodiment of FIG. FIG. 6 is a perspective view of a portion of another non-limiting blade embodiment. FIG. 34 is a partial perspective view of the FIG. 33 blade embodiment of another non-limiting outer sheath embodiment. FIG. 6 is a partial perspective view of another non-limiting blade and outer sheath embodiment. FIG. 6 is a perspective view of a portion of another non-limiting blade embodiment. FIG. 6 is a partial cross-sectional view of another non-limiting ultrasonic surgical instrument embodiment. FIG. 6 is a partial cross-sectional view of a nosepiece portion of another non-limiting surgical instrument embodiment of the present invention. FIG. 37 is a partial perspective view of the distal end of the non-limiting outer sheath and blade embodiment of FIG. FIG. 38 is a cross-sectional view of the distal portion of the outer sheath and blade embodiment shown in FIG. 37 cutting tissue. 36 illustrates the use of the surgical instrument embodiment of FIG. 36 in connection with performing a discectomy. 37 further illustrates the use of the surgical instrument embodiment of FIG. 36 in connection with performing a discectomy. FIG. 37 is a side elevational view of the surgical instrument embodiment of FIG. 36 having an optional retractable safety sheath attached to the top. FIG. 42 is a partial perspective view of the retractable safety sheath embodiment illustrated in FIG. 41 beginning to retract from the closed position. FIG. 43 is another partial perspective view of the retractable safety sheath embodiment illustrated in FIGS. 41 and 42 with the safety sheath retracted to the open position. FIG. 44 is another partial perspective view of the retractable safety sheath embodiment illustrated in FIGS. 41-43, with the safety sheath retracted to the open position. FIG. 45 is a side elevational view of a portion of the outer sheath and the safety sheath, illustrated in FIGS. 41-44, where the safety sheath is shown in cross-section in the open position. FIG. 6 is a perspective view of a portion of another non-limiting blade embodiment. FIG. 6 is a side view of a portion of another hollow outer sheath and blade configuration of another non-limiting embodiment. FIG. 6 is a cross-sectional view of another non-limiting blade embodiment. FIG. 6 is a cross-sectional view of another non-limiting blade embodiment. FIG. 6 is a cross-sectional view of another non-limiting blade embodiment. FIG. 6 is a cross-sectional view of another non-limiting blade embodiment. FIG. 6 is a partial cross-sectional view of another non-limiting outer sheath and blade embodiment. FIG. 53 is another partial cross-sectional view of the outer sheath and blade embodiment of FIG. 52 interacting with body tissue. FIG. 54 is an end cross-sectional view of the outer sheath and blade configuration shown in FIGS. 52 and 53 interacting with body tissue. FIG. 6 is a partial perspective view of another non-limiting outer sheath embodiment. FIG. 6 is a partial perspective view of another non-limiting outer sheath embodiment. FIG. 57 is a partial cross-sectional view of the outer sheath embodiment of FIG. 56, illustrating another non-limiting blade embodiment. FIG. 6 is a partial perspective view of another non-limiting outer sheath embodiment. FIG. 6 is a cross-sectional view of another non-limiting outer sheath and blade embodiment. Fig. 6 illustrates the angle between cutting edges formed on a non-limiting outer sheath embodiment. FIG. 6 is a perspective view of another non-limiting outer sheath embodiment. FIG. 62 is a cross-sectional view of the outer sheath and blade embodiment of FIG. 61. FIG. 6 is a perspective view of another non-limiting outer sheath embodiment. FIG. 64 is a cross-sectional view of the outer sheath and blade embodiment of FIG. 63. FIG. 6 is a perspective view of another non-limiting outer sheath embodiment. FIG. 66 is a cross-sectional view of the outer sheath and blade embodiment of FIG. FIG. 6 is a partial cross-sectional end view of another non-limiting outer sheath and blade configuration. FIG. 68 is a partial side cross-sectional view of the outer sheath and blade configuration of FIG. 67. FIG. 69 is a partial side view of the distal end of the outer sheath and blade configuration of FIGS. 67 and 68. FIG. 70 is a side view of a non-limiting handpiece housing embodiment attached to the outer sheath and blade configuration of FIGS. 71. A method of using the surgical instrument embodiment of FIG. FIG. 71 is another method of using the surgical instrument embodiment of FIG. FIG. 71 is another method of the surgical instrument embodiment of FIG. FIG. 6 is a partial side cross-sectional view of another non-limiting surgical instrument embodiment. FIG. 75 is a perspective view of a portion of an outer sheath and blade configuration utilized with the surgical instrument embodiment shown in FIG. 74. FIG. 76 is an end view of the outer sheath and blade embodiment of FIG. 77 is a cross-sectional end view of the sheath and blade configuration of FIGS. 75 and 76. FIG. FIG. 3 is a side view of another non-limiting ultrasonic surgical instrument embodiment. FIG. 3 is a partial cross-sectional view of a non-limiting seal embodiment between a hollow sheath and a waveguide portion of an ultrasonic device embodiment. FIG. 6 is a partial cross-sectional view of another non-limiting seal embodiment between a hollow sheath and a waveguide portion of an ultrasonic device embodiment. FIG. 6 is a partial cross-sectional view of another non-limiting seal embodiment between a hollow sheath and a waveguide portion of an ultrasonic device embodiment. FIG. 6 is a partial cross-sectional view of another non-limiting seal embodiment between a hollow sheath and a waveguide portion of an ultrasonic device embodiment. FIG. 6 is a partial cross-sectional view of another non-limiting seal embodiment between the hollow sheath and the waveguide portion of the ultrasound device before pleating in place. FIG. 84 is a partial cross-sectional view of the seal embodiment of FIG. 83 after pleating in place. FIG. 6 is a partial cross-sectional view of another non-limiting seal embodiment between a two-part hollow sheath and a waveguide portion of an ultrasonic device embodiment. FIG. 10 is a partial cross-sectional exploded view of another non-limiting seal embodiment between another two-part hollow sheath and a waveguide portion of an ultrasonic tool embodiment. FIG. 87 is a partial perspective view of a portion of the two-part hollow sheath embodiment of FIG. FIG. 6 is a partial cross-sectional view of another non-limiting seal embodiment between a hollow sheath and a waveguide portion of an ultrasonic device embodiment. FIG. 6 is a partial cross-sectional view of another non-limiting seal embodiment between a hollow sheath and a waveguide portion of an ultrasonic device embodiment. FIG. 6 is a partial cross-sectional view of another non-limiting seal embodiment between a hollow sheath and a waveguide portion of an ultrasonic device embodiment. FIG. 6 shows the initial position of two cutting edge embodiments in preparation for cutting hard tissue. FIG. 91A shows a cut edge and a second location of tissue. 91A-B cut edge and third position of tissue. 91A-C, cutting edge and tissue fourth position. FIG. 3 is a perspective view of a portion of a non-limiting cutting blade and bushing embodiment. 92 is a partial cross-sectional view of a portion of the blade and bushing of FIG. 92 inserted into the inner sheath of a non-limiting surgical embodiment. 92 is a partial cross-sectional view of a portion of the blade and bushing embodiment of FIG. 92 inserted into the inner sheath of a non-limiting surgical embodiment. FIG. 3 is a perspective view of a portion of a non-limiting cutting blade and bushing embodiment. FIG. 95 is a partial cross-sectional view of a portion of the blade and bushing embodiment of FIG. 94 inserted into the inner sheath of a non-limiting surgical embodiment. FIG. 6 is a partial perspective view of a portion of a non-limiting blade and outer sheath embodiment. FIG. 99 is a cross-sectional view of the blade and outer sheath configuration of FIG. FIG. 98 is a partial rear perspective view of a portion of the outer sheath and blade of FIG. 97. FIG. 6 is a partial rear view of a portion of another non-limiting outer sheath and blade embodiment. FIG. 6 is a partial perspective view of another non-limiting outer sheath embodiment. FIG. 100 is a cross-sectional end view of the outer sheath embodiment of FIG. 100 supporting a cutting blade embodiment therein. FIG. 6 is a perspective view of a portion of another non-limiting blade embodiment.

The holder of this application also owns the following US patent applications, filed on the same date, which are hereby incorporated by reference in their entirety:
US patent application number _____, title "ULTRASONICLY POWERED SURGICAL INSTRUMENTS WITH ROTATING CUTTING IMPLEMENT", agent serial number END 6688USNP / 090341,
US Patent Application No. _____, title "METHODS OF USING ULTRASONIC POWERED SURGICAL INSTRUMENTS WITH ROTATABLE CUTING IMPLEMENTS", Attorney Docket No. END6689USNP / 090342
No. ______, title “SEAL ARRANGEMENTS FOR ULTRASONICARY POWERED SURGICAL INSTRUMENTS”, agent reference number END 6690 USNP / 090343,
No. _____, title “LTRASONIC SURGICAL INSTRUMENTS WITH ROTATABLE BLADE AND HOLDLOW SHEATH ARRANGEENTS”, agent reference number END6691USNP / 090344,
No. ___________, title “LTRASONIC SURGICAL INSTRUMENTS WITH PARTARY ROTATING BLADE AND FIXED PAD ARRANGEMENT”, agent reference number END6693USNP / 090346,
No. __________, title “DUAL PURPOSE SURGICAL INSTRUMENT FOR CUTTING AND COAGULATING TISSUE”, agent reference number END6694USNP / 090347,
No. ______, title “OUTER SHEATH AND BLADE ARRANGEMENTS FOR ULTRASONIC SURGICAL INSTRUMENTS”, agent reference number END 6695 USNP / 090348,
No. _____, title “ULTRASONIC SURGICAL INSTRUMENTS WITH MOVING CUTTING IMPLEMENT ENT” END 6686 USNP / 090367.

  Various embodiments are directed to devices, systems and methods for tissue treatment. Numerous specific details are given to provide a thorough understanding of the overall structure, function, manufacture, and use of the embodiments described in the specification and illustrated in the accompanying drawings. However, one of ordinary skill in the art appreciates that the embodiments may be practiced without such specific details. In other instances, well-known operations, components, and elements have not been described in detail so as not to obscure the embodiments described in the specification. One skilled in the art can appreciate that the embodiments described and illustrated herein are non-limiting examples, and thus the specific structural and functional details disclosed herein may be typical, It should be understood that the scope of the embodiments is not necessarily limited, and that the scope of the embodiments is defined only by the appended claims.

  Throughout this specification, references such as “various embodiments,” “some embodiments,” “one embodiment,” or “embodiments” are specific to the particular embodiment described in connection with that embodiment. A feature, structure, or characteristic is meant to be included in at least one embodiment. Thus, phrases such as “in various embodiments”, “in some embodiments”, “in one embodiment”, or “in an embodiment” appearing in multiple places throughout this specification are not necessarily all. Do not refer to the same embodiment. Furthermore, the particular features, structures, or characteristics may be combined in any suitable manner in one or more embodiments. Thus, a particular feature, structure, or characteristic illustrated or described with respect to one embodiment may be combined, in whole or in part, without limitation, with the feature, structure, or characteristic of one or more other embodiments. Can do.

  Various embodiments provide improved ultrasonic surgical systems and instruments, as well as cutting tools and sealing mechanisms utilized therein, that are configured to cause tissue dissection, cutting and / or coagulation during surgery. Is targeted. In one embodiment, the ultrasonic surgical instrument device is configured for use in an open surgical procedure, but also has applications in other types of surgery such as laparoscopes, endoscopes, and robot-assisted procedures. Selective use of ultrasonic energy and selective replacement of cutting / coagulation tools facilitates multi-purpose applications.

  It will be appreciated that the terms “proximal” and “distal” are used herein with reference to the clinician gripping the handpiece assembly. Thus, the end effector is distal to the more proximal handpiece assembly. Furthermore, for convenience and clarity, space terms such as “upper” and “lower” are also used herein with reference to the clinician holding the handpiece assembly. However, surgical instruments are used in many orientations and arrangements, and these terms are not intended to be limiting and absolute.

Surgical System FIG. 1 illustrates a non-limiting embodiment of a surgical system 10 in schematic form. Surgical system 10 may include an ultrasonic surgical instrument assembly 100, which may include an ultrasonic generator 12 and a “built-in” ultrasonic instrument 110. As described in more detail below, the ultrasonic generator 12 is located within the housing portion 102 of the surgical instrument assembly 100 by way of the cable 14 to the ultrasonic transducer assembly 114 of the self-contained ultrasonic instrument 110. It can be connected by a slip ring assembly 150. In one embodiment, the system 10 further includes a motor control system 20, which includes a power source 22, which is coupled to a control module 24 by a cable 23, for example supplying 24VDC. The motor control module 24 may include a control module manufactured by National Instruments of Austin, Texas with model number NI cRIO-9073. However, other motor control modules can be utilized. The power source 22 may include a power source manufactured by National Instruments. However, other power sources can be used well. The power supply 22 is further connected to a motor drive 26 by a cable 25, which can also supply 24DVC here. Motor drive 26 may include a motor drive manufactured by National Instruments. The control module 24 can also be coupled to the motor drive 26 by a cable 27 to supply power thereto. A conventional foot pedal 30 or other control switch configuration may be attached to the control module 24 by a cable 31. As described in more detail below, the ultrasonic surgical instrument 100 may include a motor 190 having an associated encoder 194. Motor 190 may include a motor manufactured by National Instruments as model number CTP12ELF10MAA00. The encoder 194 is a U.S. S. It may include an encoder manufactured by Digital (Vancouver, Washington) as model number E2-500-197-IDDB. However, other motors and encoders can be used. Encoder 194 may be coupled to motor control module 24 by encoder cable 32 and motor 190 may be coupled to motor drive 26 by cable 33. The surgical system 10 can include a computer 40 that can communicate with the motor control module 24 via an Ethernet cable 42.

  As seen in FIG. 1, in various embodiments, the motor control system 20 is housed within an enclosure 21. In order to facilitate easy portability of the system, various components may be attached to the motor control system 20 by removable cable connectors. For example, the foot pedal switch 30 may be attached to a removable cable connector 37 by a cable 35 to facilitate quick attachment of the foot pedal to the control system 20. A / C power may be supplied to the power supply 22 by a conventional plug / cable 50 attached to a removable cable connector 54 attached to the cable 52. The computer 40 may have a cable 60 attached to a removable cable connector 62 that is coupled to a cable 42. The encoder 194 can have an encoder cable 70 attached to a removable connector 72. Similarly, the motor 190 can have a cable 74 attached to a removable connector 72. The removable connector 72 may be attached to the control module 24 by the cable 32, and the connector 72 may be attached to the motor driver 26 by the cable 33. Accordingly, the cable connector 72 functions to couple the encoder 194 to the control module 24 and the motor 190 to the motor drive 26. Cables 70 and 74 may be housed within a common sheath 76.

  In another embodiment, the ultrasound generator 12 and the control system 20 can be housed within the same enclosure 105. See FIG. 1A. In yet another embodiment, the ultrasonic generator 12 may be in electrical communication with the motor control system 20 via a jumper cable 107. Such a configuration may share a power data link as well as common means (code 50) for supplying power. See FIG. 1B.

  In various embodiments, the ultrasonic generator 12 may include an ultrasonic generator module 13 and a signal generator module 15. Please refer to FIG. The ultrasonic generator module 13 and / or the signal generator module 15, each of which may be integral with the ultrasonic generator 12, or provided as a separate circuit module electrically connected to the ultrasonic generator 12. (Shown in phantom lines to illustrate this option). In one embodiment, the signal generator module 15 may be formed integrally with the ultrasonic generator module 13. The ultrasonic generator 12 may include an input device 17 located on the front panel of the generator 12 console. Input device 17 may include any suitable device that generates signals suitable for programming the operation of generator 12 in a known manner. With further reference to FIG. 1 and described in further detail below, the cable 14 can be used to apply electrical energy to the positive electrode (+) and the negative electrode (−) of the ultrasonic transducer assembly 114. Of conductors.

  Various forms of ultrasonic generators, ultrasonic generator modules and signal generator modules are known. For example, such a device is disclosed in commonly assigned US patent application Ser. No. 12 / 503,770, entitled “Rotating Transducer Mount For Ultrasonic Surgical Instruments” (filed July 15, 2007), which includes: This is incorporated herein by reference in its entirety. Other such devices are disclosed in one or more of the following US patents, all of which are incorporated herein by reference; US Pat. No. 6,480,796, “Method for Improving the Start Up of an”. Ultrasonic System Under Zero Load Conditions, No. 6,537,291, “Method for Detecting a Lose in the Hand, Connected to the Ultra, No. 6”, “Method for Detecting a Loose, 6” System to Improve Acquisition of Blade Re `` sonance Frequency at Startup '', No. 6,633,234, “Method for Detecting Blade Breaking Usage Rate and / or Impedance Information,” No. 6,662,127, System ", No. 6,678,621," Output Displacement Control Using Phase Margin in an Ultrasonic Surgical Handle ", No. 6,679,899," Method for Detecting Detection ". in an Ultrasonic Handle, "No. 6,908,472," Apparator and Method for Altering Generator Functions in an Ultrasonic Surgical ", No. 6,97D No. 7,077,853, “Method for Calculating Transducer Capacitance to Determine Transducer Temperature”, No. 7,179,271, “Method for Driving an Ulti ystem to Improve Acquisition of Blade Resonance Frequency at Startup ", the same No. 7,273,483," Apparatus and Method for Alerting Generator Function in an Ultrasonic Surgical System ".

Surgical Instrument As seen in FIG. 2, the ultrasonic surgical instrument handpiece 100 may include a housing 190 that houses a motor 190, an encoder 194, a slip ring assembly 150, and a built-in ultrasonic surgical instrument 110. The housing 102 may be provided in two or more parts that are attached together by fasteners such as screws, snap mechanisms, etc., and may be made, for example, from a polycarbonate material. The motor 190 may include a stepper motor manufactured, for example, by National Instruments as model number CTP12ELF10MAA00. However, other motors may be utilized to produce a “total” rotational movement of the embedded ultrasonic surgical instrument 110 relative to the housing 102, for example, between about 1 and 6000 rpm. The encoder 194 converts the mechanical rotation of the motor shaft 192 into electrical pulses that provide speed and other motor control information to the control module 24.

  The self-contained ultrasonic surgical instrument 110 may include a surgical instrument manufactured and sold by Ethicon Endo-Surgery with model number HP054. However, other ultrasonic instruments can be used well. The term “built-in” as used herein means that an ultrasonic surgical instrument can itself be effectively used as an ultrasonic surgical instrument, other than when used with surgical instrument 100. Is understood as meaning. As illustrated in detail in FIG. 3, the ultrasonic surgical instrument 110 includes a housing 112 that supports a piezoelectric ultrasonic transducer assembly 114 for converting electrical energy into mechanical energy. The conversion produces a longitudinal oscillating motion at the end of the transducer assembly 114. The ultrasonic transducer assembly 114 may include a stack of ceramic piezoelectric elements, with an operating zero point located at any point along the stack. An ultrasonic transducer assembly 114 may be mounted between the two cylinders 116 and 118. In addition, the cylinder 120 may be attached to the cylinder 118, which in turn is attached to the housing at another operating zero point 122. The horn 124 may also be attached to the coupler 126 on one side with a zero point on the other side. The blade 200 can be secured to the coupler 126. As a result, the blade 200, along with the ultrasonic transducer assembly 114, vibrates longitudinally at ultrasonic frequencies. The end of the ultrasonic transducer assembly 114 achieves maximum motion with a portion of the stack constituting the stationary node when the ultrasonic transducer assembly 114 is driven at maximum current at the transducer resonant frequency. . However, the current providing maximum motion varies from instrument to instrument and is a value stored in the instrument's non-volatile memory for use by the system.

  The portions of the ultrasonic instrument 110 can be designed such that the combination vibrates at the same resonant frequency. In particular, the elements may be adjusted so that the resulting length of each such element is half or a multiple of the wavelength. Longitudinal longitudinal motion amplifies as the diameter of the acoustic mounting horn 124 closer to the blade 200 decreases. Accordingly, the blade / coupler in addition to the horn 124 may be shaped and dimensioned to amplify blade motion and provide ultrasonic vibration, corresponding to the rest of the acoustic system, which is an acoustic mounting close to the blade 200 A maximum back and forth motion of the end of the horn 124 is generated. The 20-25 micrometer movement in the ultrasonic transducer assembly 114 can be amplified by the horn 124 to a blade movement of about 40-100 micrometers.

  When power is applied to the ultrasonic instrument 110 by operation of the foot pedal 30 or other switch configuration, the control system 20 causes the blade 200 to vibrate longitudinally at approximately 55.5 kHz, for example, and the longitudinal momentum is determined by the user. It varies proportionally with the amount of drive power (current) applied that is selected to be adjustable. When relatively high cutting power is applied, the blade 200 may be designed to move longitudinally in the range of about 40-100 micrometers at ultrasonic vibration speeds. Such ultrasonic vibrations of the blade 200 generate heat when the blade contacts the tissue, i.e., the mechanical energy of the blade 200 in which the acceleration of the blade 200 moves through the tissue is very narrow and localized. It converts to heat energy in the area. This local heat results in clotting in a narrow zone, which reduces or eliminates bleeding in small defects, such as less than 1 millimeter in diameter. The cutting efficiency of the blade 200, as well as the degree of hemostasis, will vary depending on the level of drive power applied, the cutting speed or force applied to the blade by the surgeon, the nature of the tissue type, and the vascular distribution of the tissue.

  As seen in FIG. 2, the ultrasonic instrument 110 is supported within the housing 102 by a tail drive adapter 130 and a distal handpiece adapter 134. Tail drive adapter 130 is rotatably supported within housing 102 by proximal bearing 132 and is non-rotatably coupled to output shaft 192 of motor 190. Please refer to FIG. The tail drive adapter 130 may be pressed onto the housing 112 of the ultrasonic instrument 110 or attached to the housing 112 by, for example, a fixing screw or adhesive. The distal handpiece adapter 134 may be pressed onto the distal end 113 of the handpiece housing 112 or otherwise attached thereto by a securing screw or adhesive. The distal handpiece adapter 134 is rotatably supported within the housing 102 by a distal bearing 136 mounted within the housing 102.

  When power is applied to the motor 190, the motor 190 applies a "full rotational motion" to the handpiece 110, which causes the ultrasonic surgical instrument 110 and the blade 200 to rotate about the central axis A-A. As used herein, the term “total rotational motion” is distinguished from “twisted ultrasonic motion” that can be achieved in utilizing a non-uniformly formed ultrasonic blade. The term “total rotational motion”, in contrast, encompasses rotational motion that is not limited to that generated by operation of the ultrasonic transducer assembly 114.

  A slip ring assembly 150 may be utilized to provide power to the ultrasonic instrument 110 from the ultrasonic generator 12. As seen in FIG. 2, the conductors 151, 152 are coupled to the ultrasonic transducer assembly 114 and extend through the hollow stem 132 of the tail drive adapter 130. The hollow stem 132 is attached to the drive shaft 192 of the motor 190 and rotates freely within the slip ring assembly 150. The first internal contact 154 is attached to the hollow stem 132 so as to rotate and move together about the axis AA. The first inner contact 154 is positioned to rotatably contact an outer contact 156 secured within the slip ring assembly 150. The contacts 154, 156 may be provided in the form of concentrically arranged rings. Conductors 157 and 158 are connected to a fixed external contact 156 to form the generator cable 14. Conductors 191 and 193 are attached to the motor to form motor cable 74, and conductors 195 and 197 are attached to encoder 194 to form encoder cable 70. The rotation of the motor shaft 192 causes the tail drive adapter 130 and the ultrasonic instrument 110 attached thereto to rotate about the axis A-A. The rotation of the motor drive shaft 192 also causes the internal contact 154 to rotate. The ultrasonic signal from the ultrasonic generator 12 is transmitted to the internal contact 154 by contact or “electrical communication” between the internal contact 154 and the external contact 156. These signals are transmitted to the ultrasonic transducer assembly 114 by conductors 151, 152. In other alternative embodiments, the slip ring assembly may utilize the use of conventional pogo pins that engage concentric ring contacts. Other slip ring configurations can also be utilized.

  Various embodiments also include a distal nosepiece 160 that can be removably attached to the distal end 103 of the housing 102 by a fastener 161. Please refer to FIG. One or more shim members 162 may be positioned between the distal end 103 and the nosepiece 160 to facilitate concentric attachment between the housing 102 and the nosepiece 160. The nosepiece 160 may be made from stainless steel or polycarbonate, for example. In various embodiments, the distal end 202 of the blade 200 extends through a hollow coupler section 210 that is pivoted within the inner sheath seal 212. Inner sheath seal 212 may include, for example, polytetrafluoroethylene (“PTFE”) to form a substantially fluid tight and / or air tight seal between coupler section 210 and nosepiece 160. To function. Also in the embodiment of FIG. 4, the inner sheath 220 may be attached to the hollow coupler section 210, for example, by welding, or the hollow coupler section 210 may include an integral part of the inner sheath 220. In one embodiment, the blade pin / torque member 216 may extend laterally through the blade member 200 and the hollow coupler section 210 to facilitate movement of the inner sheath 220 and the blade member 200. A bushing 214 having one or more vents may be pivoted around the blade 200 to acoustically isolate the blade 200 from the inner sheath 220. The blade member 200 may have a proximal end 201 that is internally threaded and adapted to removably engage the threaded portion of the coupler 126. To facilitate clamping of the blade 200 to the coupler 126, a clamping hole 108 (FIG. 2) is provided through the housing 102 and a tool (eg, an Allen wrench) is inserted therethrough into the hole 131 of the tail drive adapter 130. Preventing rotation of the ultrasonic surgical instrument 110 and the coupler 126 attached thereto. Once the blade 200 is screwed onto the coupler 126, the user removes the Allen wrench or other tool from the holes 108, 131 and inserts a threaded plug (not shown) into the hole 108 through which fluid / debris passes. Entering the housing 102 can be prevented.

  In various embodiments, the outer sheath 230 may be coaxially aligned with the inner sheath 220 and the blade member 200, such as by welding, brazing, overmolding, or press fitting, to the distal end of the nosepiece 160. 163 may be attached. As seen in FIG. 4, a suction portion 240 may be attached to the nosepiece 160 to communicate with the hollow outer sheath 230. The flexible tube 242 may be attached to the suction portion 240 and communicate with a collection container 243 connected to a vacuum source, generally indicated as 244. Thus, the outer sheath 230 forms a suction path that extends around the inner sheath 220 starting at the distal tip of the outer sheath 230 and exiting through the suction portion 240. Those skilled in the art will recognize that alternative suction paths are also possible. In addition, in another embodiment, the inner sheath 220 is omitted.

  Various embodiments of the surgical system 10 provide the ability to selectively apply ultrasonic axial motion to the blade 200 and similarly to full rotational motion to the blade 200. If desired, the clinician may simply activate the ultrasonic transducer assembly 114 without activating the motor 190. In some cases, instrument 100 can be used in an ultrasound mode, simply as an ultrasound instrument. The frequency range for longitudinal ultrasonic motion can be, for example, about 30-80 kHz. Similarly, the clinician may desire to activate the motor 190 without activating the ultrasonic transducer assembly 114. Thus, the entire rotational motion is applied to the blade 200 in the rotational mode without applying longitudinal ultrasonic motion thereto. The overall rotational speed can be, for example, about 1 to 6000 rpm. In other applications, the clinician may desire to use the instrument 100 in ultrasonic and rotational modes, and the blade 200 is used for longitudinal ultrasonic motion from the transducer assembly 114 and total rotation from the motor. Experience exercise. Oscillating motions of 2-10 revolutions per cycle (720-3600 °) or continuous unidirectional rotations can be achieved. Those skilled in the art will recognize that various embodiments of the surgical system 10 can be effectively utilized in connection with arthroscopic and other surgical applications.

  At least one non-limiting embodiment can further include a control arrangement 170 on the housing 102. Please refer to FIG. The control configuration 170 may communicate with the control module 24 via a multiconductor cable 171. The control configuration 170 may include a first button 172 for activating / deactivating “duplex” modes including “ultrasonic mode” and “rotation mode”. In such a configuration, the control module 24 may be pre-programmed to provide a prescribed amount of total rotational movement to the blade 200. The control arrangement 170 may further include a second button 174 to activate / deactivate the rotation mode without activating the ultrasound mode, and thus to disconnect without hemostasis. The control arrangement 170 may also include a third button 176 to activate / deactivate the “coagulation mode”, where the motor 190 is driven to preset the rotation direction, and then “stop” or deactivate, This exposes the ultrasonic blade surface at the distal end of the outer sheath 240, which will be described in more detail below. Also in this mode, the ultrasound transducer assembly 114 may be driven to provide spot clotting, and in another embodiment, the clinician simply activates the spot clotting button 77, which causes the ultrasound transducer assembly 114. May be activated for a defined period of time, eg, 5 seconds. The control arrangement may further include a button 178 for switching between ultrasound and rotation modes. Various non-limiting embodiments can provide any of the functions / modes described above without departing from the spirit and scope of the various non-limiting embodiments disclosed herein, as well as equivalent structures. May be combined and controlled by one or more buttons.

  One skilled in the art will know that the housing member 102 and the mounting adapters 130 and 134 operably hold various different types and shapes of ultrasonic handpieces that can be used separately from the surgical instrument 100. Understand that it can be configured as follows. Accordingly, the control system 20 and the instrument 100 can be used without the ultrasonic handpiece 110 without departing from the various non-limiting embodiments disclosed herein, as well as the spirit and scope of each of these equivalent structures. , Provided in “kit form”, allowing the purchaser to insert the existing ultrasonic handpiece into the interior.

  FIGS. 6 and 7 illustrate another surgical instrument 300, with like numbers used previously to describe the various embodiments described above are used to designate similar components. . In these embodiments, surgical instrument 300 includes a housing 302 that houses a transducer assembly 314 attached to an ultrasonic horn 324. The ultrasonic horn 324 can be coupled to the proximal end 201 of the blade 200 in the manner described above. Ultrasonic horn 324 may be rotatably supported within housing 302 by distal bearing 336. The nosepiece 160 may be attached to the housing 302 by the fastener 161 in the manner described above.

  In this embodiment, the ultrasonic transducer assembly 314 has a magnet 316 embedded therein or otherwise attached to form an integral motor rotor, generally designated 320. A motor retaining ring 330 is mounted in the housing 302 as shown. The conductors 332 and 334 are attached to the motor fixing ring 330, extend through the common sheath 76, and are attached to the motor cable 33 in the control system 20 described above. A hollow shaft 340 extends through the motor roller 320 and forms a path for the conductors 151, 152. The conductors 151, 152 are coupled to the ultrasonic transducer assembly 314 and the internal contact 154. Internal contact 154 is attached to a portion of hollow shaft 340 that extends rotatably within slip ring assembly 150 that is also supported within housing 302. Hollow shaft 340 is rotatably supported within housing 302 by proximal bearing 342. The slip ring assembly 150 includes a fixed external contact 156 fixed within the housing 302 (ie, non-rotatable) and coupled to conductors 157, 158 that form the generator cable 14 described above. When electric power is supplied to the motor stator 330, this causes the rotor 320 and the integrated ultrasonic transducer 314 to rotate about the axis AA. The ultrasonic signal from the ultrasonic generator 12 is transmitted to the internal contact 154 by rotational contact or electrical communication between the internal contact 154 and the external contact 156. These signals are transmitted to the ultrasonic transducer assembly 314 by conductors 151, 152. Surgical instrument 300 includes a control configuration of the type described above and can be used in the various modes described above. Suction can be applied through the port 240 between the blade 200 and the outer sheath 230. The collection container 243 and the suction source 240 may be attached to the port 240 by a tube 242. As described in more detail below, the distal end of the blade is exposed through a window at the distal end of the outer sheath 230 to expose the blade to tissue.

  FIG. 8 illustrates another surgical instrument 400, where like numbers previously used to describe the various embodiments described above are used to designate similar components. In these embodiments, the surgical instrument 400 includes a housing 302 that houses an ultrasonic transducer assembly 314 attached to an ultrasonic horn 324. The ultrasonic horn 324 can be coupled to the proximal end 201 of the blade 200 in the manner described above. Ultrasonic horn 324 may be rotatably supported within housing 302 by distal bearing 336. The nosepiece 160 may be attached to the housing 302 by the method described above.

  In this embodiment, the brushed motor 410 is integrally attached to the ultrasonic transducer assembly 314. As used herein, “integrated attached” means attached directly to the ultrasound transducer assembly 314 or otherwise formed therewith so that it moves together. To do. When used in connection with attachment to the brushed motor 410 and the ultrasonic transducer assembly 314, the term “integrated attached” refers to a configuration in which the ultrasonic transducer assembly is attached to the motor via a drive shaft configuration. Does not include. Also in this embodiment, the magnet 426 is provided in a securing ring 420 that is secured in the housing 302. Conductors 432 and 434 extend through a hollow shaft 340 attached to the brushed motor 410. Hollow shaft 340 is rotatably supported within housing 302 by proximal bearing 342. Motor conductor 432 is attached to first internal motor contact 436, and motor conductor 434 is attached to second internal motor contact 438. First internal motor contact 436 and die 2 motor internal contact 438 are supported on the portion of hollow shaft 340 that extends into the slip ring assembly, generally designated 450. Slip ring assembly 450 is fixed within housing 302 (ie, non-rotatable) and includes a first external motor contact 440 coupled to conductor 441 and a second external motor contact 442 coupled to conductor 443. The conductors 441 and 443 form the motor cable 74 described above. If the clinician desires to apply full rotational motion to the ultrasonic transducer assembly 314 and ultimately to the blade 200, the clinician causes the motor drive 26 to supply power to the brushed motor 410.

  In this embodiment, the conductors 151, 152 are attached to the ultrasonic transducer assembly 314, extend through the hollow shaft 340, and are coupled to internal transducer contacts 154 attached to the hollow shaft 340. Slip ring assembly 450 includes a fixed external transformer contact 156 coupled to conductors 157, 158 forming generator cable 14, as described above. When power is supplied to brushed motor 410, this causes motor 410, ultrasonic transformer assembly 314, and motor shaft 340 to rotate about axis A-A. The ultrasonic signal from the ultrasonic generator 12 is transmitted to the internal contact 154 by rotational sliding contact or electrical communication between the internal contact 154 and the external contact 156. These signals are transmitted to the ultrasonic transducer assembly 314 by conductors 151, 152. Surgical instrument 400 includes a control configuration of the type described above and can be used in the various modes described above. As described above, it will be appreciated that the instrument 400 may be used in rotational mode, ultrasonic mode, rotational and ultrasonic mode (“dual mode”) or coagulation mode. Suction can be applied through the port 240 between the blade 200 and the outer sheath 230. The collection container 243 and the suction source 240 may be attached to the port 240 by a tube 242. As described in more detail below, the distal end of the blade is exposed through a window at the distal end of the outer sheath 230 to expose the blade to tissue.

  FIGS. 9-13 illustrate another surgical instrument 500, where like numbers previously used to describe the various embodiments described above are used to designate similar components. In these embodiments, the surgical instrument 500 includes a housing 302 that houses a transducer assembly 530 attached to an ultrasonic horn 324. The ultrasonic horn 324 can be coupled to the proximal end 201 of the blade 200 in the manner described above. Ultrasonic horn 324 may be rotatably supported within housing 302 by distal bearing 336. The nosepiece 160 may be attached to the housing 302 by the method described above.

  This embodiment includes a motor 510 that may include a stepper motor of the type and configuration described above and may have an encoder portion associated therewith that communicates with the control module 24 described above. The motor 510 may receive power from the motor drive 26 through conductors 511, 512 that include a motor cable 74 that extends through a common sheath 76. The motor 510 has a hollow motor shaft 520 attached thereto and extending through the slip ring assembly 150. Hollow drive shaft 520 is rotatably supported within housing 302 by proximal bearing 342. The slip ring assembly 150 includes a fixed external contact 156 fixed within the housing 302 (ie, non-rotatable) and coupled to conductors 157, 158 that form the generator cable 14 described above. The inner contact 154 is mounted on the hollow drive shaft 520 and is in electrical contact or communication with the outer contact 156. Conductors 151, 152 are attached to the internal contact 154, extend through a hollow drive shaft 520, and are coupled to the ultrasonic transducer assembly 530.

  In various embodiments, the hollow drive shaft 520 is generally designated as 540 to facilitate assembly and also to acoustically isolate the motor from the ultrasonic transducer assembly 530. May be removably coupled to the ultrasonic transducer stack 530. As seen in FIGS. 9, 11, and 12, the coupling assembly 540 may include a thin plate member 542 that is attached to the distal end 521 of the hollow drive shaft 520. The thin plate member 542 may be made from a material that has a relatively low stiffness in the axial direction and a high stiffness in rotation. Please refer to FIG. For example, the thin plate member 542 may be made from 0.020 inch (0.008 cm) thick aluminum 7075-T651 and attached to the distal end 521 of the hollow drive shaft 520 by, for example, a press fit or braze. Good. The coupling assembly 540 may further include a proximal end portion or flange portion 531 of the ultrasonic transformer assembly 530. Proximal end portion 531 may include a flange made from stainless steel attached to ultrasonic transducer assembly 530, for example, by bolts or by other connections. As seen in FIG. 11, the end 531 has a hole 532 sized to receive a thin plate member 542 therein. In various embodiments, the thin plate member 542 may be sized to be pushed into the hole 532 so that rotation of the thin plate member 542 about the axis AA causes the axis AA to rotate. A rotation of the ultrasonic transducer assembly 530 about the center occurs. In other embodiments, a separate fastening plate (not shown) or snap ring (not shown) or snap mechanism (not shown) is non-rotatably engaged with the end 531 of the ultrasonic transducer assembly 530. A thin plate member 542 may be provided to hold. Such a configuration functions to minimize the transmission of acoustic vibrations from the ultrasonic transducer assembly to the motor.

  14 and 15 illustrate another thin plate member 542 'that may be utilized. In this embodiment, thin plate member 542 ′ has a plurality of radial notches 544 provided therein to form radial tabs 546. The holes 532 are notched (not shown) to match the radial tabs 546 therein. Such a configuration may reduce the moment force applied to the shaft 520. By utilizing thin plate members 542, 542 ', the amount of acoustic vibration transmitted from the ultrasonic transducer assembly 530 to the drive shaft 520 can be minimized.

  When power is supplied to the motor 510, the drive shaft 520 rotates about axis AA, which also causes the transducer assembly 530 to rotate about axis AA. When the clinician desires to drive the ultrasonic transducer assembly 530, power is supplied from the ultrasonic generator 12 to the stationary contact 156 of the slip ring assembly 150. Power is transferred to the ultrasonic transducer assembly 530 by rotational sliding contact or electrical communication between the inner contact 154 and the outer contact 156. These signals are transmitted to the ultrasonic transducer assembly 530 by conductors 151, 152. Surgical instrument 500 includes a control configuration of the type described above and can be used in the various modes described above. As described above, it will be appreciated that the instrument 400 may be used in rotational mode, ultrasonic mode, rotational and ultrasonic mode (“dual mode”) or coagulation mode. Suction can be applied through the port 240 between the blade 200 and the outer sheath 230. The collection container 243 and the suction source 240 may be attached to the port 240 by a tube 242. As described in more detail below, the distal end of the blade is exposed through a window at the distal end of the outer sheath 230 to expose the blade to tissue.

  FIG. 16 illustrates another surgical instrument 600, where like numbers used previously to describe the various embodiments above are used to designate similar components. In these embodiments, surgical instrument 600 includes a housing 302 that houses a transducer assembly 314 attached to an ultrasonic horn 324. In this embodiment, the transformer assembly 314 and the ultrasonic horn 324 are attached to a PZ housing 602 that is rotatably supported within the housing 302 by a distal bearing 336. The ultrasonic horn 324 can be coupled to the proximal end of the blade 200 in the manner described above. The nosepiece 160 may be attached to the housing 302 by the fastener 161 in the manner described above.

  This embodiment includes a motor 510, which may include a stepper motor of the type and configuration described above. The motor 510 may have an encoder associated therewith, which communicates with the control module 24 (FIG. 1) as described above. The motor 510 may receive power from the motor drive 26 (FIG. 1) through conductors 511, 512 that include a motor cable 74 that extends through the common sheath 76. The motor 510 has a hollow motor shaft 520 attached thereto and extending through the slip ring assembly 150. Hollow drive shaft 520 is rotatably supported within housing 302 by proximal bearing 342.

  The slip ring assembly 150 includes a fixed external contact 156 fixed within the housing 302 (ie, non-rotatable) and coupled to conductors 157, 158 that form the generator cable 14 described above. The inner contact 154 is mounted on a rotatable hollow drive shaft 520 and is in electrical contact with or in communication with the outer contact 156. Conductors 151, 152 are attached to the internal contacts 154, extend through a hollow drive shaft 520, and are coupled to the ultrasonic transducer assembly 314. In various embodiments, the hollow drive shaft 520 is coupled, generally designated as 540, to facilitate assembly and to acoustically isolate the motor 510 from the ultrasonic transducer assembly 314. The assembly may be removably coupled to the PZT housing 602. The coupling assembly 540 may include a thin plate member 542 attached to the distal end 521 of the hollow drive shaft 520. As described above, the thin plate member 542 may be made from a material that has a relatively low stiffness in the axial direction and a high stiffness in rotation. PZT housing 602 has a proximal end 604 with a hole 603 sized to receive a thin plate material 542 therein. In various embodiments, the thin plate member 542 may be sized to be pushed into the hole 603 such that rotation of the thin plate member 542 about the axis AA causes the axis AA to rotate. A rotation of the central PZT housing 602 and the ultrasonic assembly 314 and ultrasonic horn 324 occurs. In other embodiments, a separate fastening plate (not shown) or snap ring (not shown) or snap mechanism (not shown) is thin so as to non-rotatably engage the proximal end 604 of the PZT housing 602. A plate member 542 may be provided to hold. This embodiment also utilizes the thin plate member 542 'described above.

  When power is supplied to motor 510, drive shaft 520 rotates about axis A-A, which also causes PZT housing 602 and ultrasonic transducer assembly 314 to rotate about axis A-A. When the clinician desires to drive the ultrasonic transducer assembly 314, power is supplied from the ultrasonic generator 12 to the stationary contact 156 of the slip ring assembly 150. Power is transferred to the ultrasonic transducer assembly 314 by rotational sliding contact or electrical communication between the inner contact 154 and the outer contact 156. These signals are transmitted to the ultrasonic transducer assembly 314 by conductors 151, 152. Surgical instrument 500 includes a control configuration of the type described above and can be used in the various modes described above. As described above, it will be appreciated that the instrument 400 may be used in rotational mode, ultrasonic mode, rotational and ultrasonic mode (“dual mode”) or coagulation mode. Suction can be applied through the port 240 between the blade 200 and the outer sheath 230. The collection container 243 and the suction source 240 may be attached to the port 240 by a tube 242. As described in more detail below, the distal end of the blade is exposed through a window at the distal end of the outer sheath 230 to expose the blade to tissue.

  In order to reduce the overall size of the housing 302 utilized in each of the instruments 300, 400, 500 and 600, the ultrasonic transducer assembly utilized in each of these instruments is physically longer in length. It can be replaced with a short half-wave converter.

Ultrasonic blade and sheath embodiments Current arthroscopic tools include punches, reciprocating shavers, and radio frequency (RF) drives. Mechanical devices such as punches and shavers tend to cause minimal tissue damage, but in some cases may leave a rough cutting line that is undesirable. The RF driven blade leaves a smoother cutting line and can cauterize large areas of soft tissue. However, such devices can cause greater tissue damage than pure mechanical instruments. The various non-limiting surgical instrument embodiments described above provide an advantageous host over conventional RF-driven surgical instruments as well as conventional mechanical shavers that utilize rotating tissue cutting members. Additional benefits can be realized by utilizing the unique and novel blade and sheath configurations of various non-limiting embodiments, as described in more detail below.

  17-21 illustrate one form of blade 200 and outer sheath 230 that may be utilized in connection with the various surgical instruments described above. As seen in these figures, the blade 200 may have a distal end 700 and the outer sheath 230 may have a distal end 720. The blade 200 may be made, for example, from titanium, and the outer sheath 230 may be made, for example, from polyetheretherketone (“PEEK”) Ultem®, or stainless steel. As described above, the blade 200 may have a waveguide or proximal end configured to be attached to the ultrasonic horn 324 (FIGS. 6-10 and 16) by screwing or otherwise. . The distal end 700 of the blade 200 may have a curved tip 702 formed at the top. The curved tip 702 can have an arcuate top section 704 having a cutting edge 706 formed on each lateral side 705. Cutting edge 706 may end in a distal direction with a common, substantially pointed distal end 708. The pointed distal end 708 may be relatively blunt, or the pointed distal end 708 may have a relatively sharp point. As seen in FIG. 20, the pointed distal end 708 may be curved inwardly about the central axis AA of the blade. As shown in FIG. 19, in various embodiments, the cutting edges 706 may not intersect each other and may be separated by a central portion 707. As seen in FIG. 20, the blade 200 may have a narrower neck 710 that projects distally from the waveguide or proximal blade portion 712. Node 714 may be formed in the region where neck 710 protrudes from proximal portion 712.

  As seen in FIG. 17, the outer sheath 230 also has a distal end 720 having a window or opening 722 formed therein, exposing the distal end 700 of the blade 200. As further seen in FIG. 17, the outer sheath 230 can include a hollow cylinder having a substantially blunt end 724. In various embodiments, the window 722 extends over half of the circular cross section of the sheath 230. Such a window configuration forms an arcuate shelf 725 that extends around the blunt end 724. In various embodiments, the outer sheath 230 can be made of, for example, polyetheretherketone (“PEEK”), Ultem®, or stainless steel. To prevent metal tube contact between the cutting edge 706 of the distal end 700 of the blade 200 and the shelf 725, a polymer fender 726 is attached around the shelf 724, for example, by an adhesive or a T-slot. May be. See FIG. 726 may be made, for example, from Teflon® or other lower or “low friction” material. The fender 726 may be sized to produce an interference fit with the cutting edge 706 and the pointed distal end 708, for example, 0.005 inches.

  In use, the blade 200 is rotated about the central axis A-A within the outer sheath 230 and introduced into the tissue, as described above, the tissue is between the inner sheath 220 (FIG. 4) and the outer sheath 230. Is pulled into the window 722 by the means of suction applied thereto. The tissue that is drawn into the window 722 is then cut as the cutting edge 706 is rotated past the fender 726, and the cut tissue may pass between the inner sheath 220 and the outer sheath 230, Through the suction port 240 (FIGS. 4, 6-10, and 16), it exits into the collection container 243 (FIGS. 4, 6-10, and 16).

  In another embodiment, the axial suction path 730 can be provided through the neck 710 of the blade 200. See FIG. The axial suction path 730 may communicate with the lateral suction path 732 in the region of the node 714. Accordingly, the cut tissue passes through the pathways 730 and 732, exits between the inner sheath 220 and the outer sheath 230, and passes through the suction port 240 (FIGS. 4, 6 to 10 and 16) to the collection container 243 (FIGS. 4 and 6). To 10 and 16). FIG. 21 illustrates another embodiment, and the two outlet paths 734, 736 communicate with the axial path 730 and extend at an angle therefrom. In various embodiments, the outlet paths 734, 736 may extend from the axial path 730 at an angle 738, such as 45 °, for example. Such a configuration may function to reduce impedance and power loss during ultrasound activation, but this may otherwise occur from water drawn through the window 722 of the outer sheath 230.

  In use, the clinician may choose to rotate the blade 200 within the outer sheath 230 without applying ultrasonic motion thereto. The clinician may also choose to apply ultrasonic motion to the rotating blade, or the clinician may desire to apply ultrasonic motion to the stop (non-rotating) blade and within the window 722. Use the portion of the blade that is exposed to coagulate the tissue.

  FIG. 22 illustrates the use of the blade 200 in conjunction with an outer sheath 230 having a distal end 750 that includes a distally protruding nose section 752. In various embodiments, the nose section 752 may have an arcuate width “W” that includes approximately 10-30% of the periphery of the distal end 750 of the outer sheath 230. The nose section 752 may protrude distally from the end of the distal end 750 of the sheath 230 by a length “L” that may be, for example, approximately 0.25 inches. In another embodiment, a low friction fender or guard (not shown) may be applied to the side 753 of the nose section 752 as needed. These embodiments may operate in a similar manner as the previous embodiments. However, this embodiment adds the ability to cut tissue with the exposed tip. As in other embodiments, the clinician may apply a pre-rotation motion to the blade 200 without or by ultrasonic motion. In another alternative method of use, the exposed tip 708 and the partially exposed cutting edge 706 can be used to cut tissue when the blade is not rotating or vibrating.

  Figures 23-24 illustrate another non-limiting blade and other sheath embodiments. In this embodiment, the blade 200 has a distal end 760 that is substantially similar to the distal end 700 of the blade configuration described above. However, the distal blade portion 760 does not bend inward to the same degree so that the blade tip 762 does not intersect the central axis AA. See FIG. As seen in FIG. 23, the window 722 ′ of the distal end 720 of the outer sheath 230 does not extend the entire distance from the end wall 725 to the blunt tip 724. Thus, in this embodiment, the blunt tip 724 includes a nose that extends by more than 90 ° and less than 180 ° (ie, the angle “A” in FIG. 23A is more than 90 ° and less than 180 °).

  Figures 25 and 26 show another non-limiting blade embodiment. In this embodiment, blade 200 'may be substantially similar to blade 200 or any of the other blades described herein. In this embodiment, the distal end 700 'has a non-planarized upper surface 705'. Such non-planarized surface 705 ′ creates a higher frictional force between the distal end 700 ′ of the blade 200 ′ and the tissue, causing the tissue to move to the distal end of the outer sheath 230 (FIG. 26). Pull into window 722 'of 720. By drawing more tissue into the window 722, the front cutting edge 706 'of the blade 200' may be more likely to cut the tissue cleanly. In various embodiments, for example, the non-planarized surface may be formed by nicking, or the top surface may be coated with a hard material such as diamond.

  Figures 27-29 illustrate another non-limiting blade embodiment. In this embodiment, the blade 200 ″ may be substantially similar to the blade 200 described herein. In this embodiment, the distal end 700 ″ rotates the blade 200 ″ within the outer sheath 230. In doing so, it has a series of radially extending cutting teeth 707 projecting outwardly from the top surface 705 "to draw and cut tissue.

  30, 31 and 32A-D illustrate another non-limiting blade and outer sheath embodiment. During the use of various instruments that utilize a blade that is rotatable within an outer sheath, a situation arises where tissue can be “evacuated” from the sheath window as the blade rotates inside. This can lead to a reduction in the cutting speed because the tissue is sufficiently captured and not maintained between the cutting edges. The blade 800 of this embodiment addresses such potential drawbacks.

  As seen in FIG. 30, the blade 800 may be substantially the same as the blade 200 except for the differences noted herein. In particular, the blade 800 may include a neck 803 that terminates at the distal end 810. The distal end 810 can have a slightly curved tip 812. A series of teeth 817 can be provided on at least one lateral side 813 or 815 of the distal end 810. In the embodiment shown in FIGS. 32A-D, teeth 817 and 819 are formed on lateral sides 813, 815 of distal end 810. The distal end 810 further has a slightly domed top 821. In the embodiment shown in FIGS. 30-32D, the teeth 817 include relatively sharp points that define a series of arcuate openings 823 therebetween. The teeth 819 also include a relatively sharp point with a series of arcuate openings 825 therebetween. As shown in FIG. 30, an axial suction path 805 can be provided through the neck 803 of the blade 800. The axial suction path 805 may communicate with the lateral suction path 807 in the area of the node 808. Thus, by the method described above, the cut tissue passes through pathways 805, 807, exits between the inner sheath (not shown) and outer sheath 850, and exits to the collection container through the suction port. Other suction path configurations can also be used successfully.

  The outer sheath 850 may be substantially similar to the outer sheath 230 described above and has a distal sheath tip 852 attached thereto, which has a window or opening 854 formed therein. , Exposing the distal end 810 of the blade 800. See FIG. The outer sheath 850 can include, for example, a hollow cylinder made from stainless steel. In various embodiments, the window 854 extends approximately half of the circular cross section of the sheath 850 and forms a blade opening 858 therein. The distal sheath tip 852 can be made from a metal, such as stainless steel, such that a relatively sharp cutting edge 860 extends around the blade opening 858. For illustrative purposes, the sharp cutting edge 860 has a first lateral cutting edge 862 and a second lateral cutting edge 864.

  32A-D illustrate the sequential rotation of the blade 800 within the outer sheath 850. Turning first to FIG. 32A, the blade 800 is shown as rotating in a counterclockwise “CCW” direction. As shown, the cutting teeth 817 on the first lateral side 813 of the blade 800 shear tissue (not shown) between the teeth 817 and the first lateral cutting edge 862 of the cutting edge 860. Positioned to do. When in this position, the arcuate opening 823 between the teeth 817 is generally exposed to form a first lateral suction path 870 between the blade 800 and the distal sheath tip 852, Tissue can be drawn into the interior from aspiration applied through aspiration path 805 (FIG. 30). As rotation continues, the dome-shaped information portion 821 of the blade 800 covers the opening 854 of the distal sheath tip 852 so that the suction path for tissue to enter the opening 854 is not exposed. As the blade continues to rotate, FIG. 32C shows that the arcuate opening 825 between the teeth 819 as a whole forms a second lateral suction path 872 between the second lateral cutting edge 864 and the blade 800. And allowing the tissue to be pulled inside. As the blade 800 continues to rotate counterclockwise, the third suction path 874 is exposed, allowing tissue to be further drawn into the opening 854. Thus, such a configuration allows for sequential opening of the blade opening 858 from one lateral side to another and facilitates better tissue cutting. In use, the clinician may choose to rotate the blade 800 within the outer sheath 850 without applying ultrasonic motion thereto. The clinician may also choose to apply ultrasonic motion to the rotating blade, or the clinician may desire to apply ultrasonic motion to the stop (non-rotating) blade and the opening 854 The portion of the blade that is exposed inside is used to coagulate the tissue.

  FIGS. 33 and 34 illustrate another blade embodiment 880 that may be substantially the same as blade 200 except for the differences noted below. In particular, the blade 880 can include a waveguide or proximal portion 882 that terminates in a distal tissue cutting portion 884. The proximal end 882 of the blade 880 can be configured to be screwed or otherwise attached to the ultrasonic horn of any of the various embodiments described above. The distal tissue cutting portion 884 can have opposing arcuate channels 886, 888 formed therein. The first arcuate channel 886 may define a first cutting edge 890 and the second arcuate channel 888 may define a second cutting edge 892. This blade embodiment may be used in connection with any of the outer sheaths described above. In the illustrated embodiment, a hollow outer sheath 900, which can be similar to the sheath 230, for example, is utilized, including a round or blunt nose portion 902 and a distal sheath tip 901 having a window 904. The hollow outer sheath 900 can be made of, for example, stainless steel, and the distal sheath tip 901 can be made of, for example, a metal such as stainless steel. Window 904 is an arcuate cutting edge that cooperates with cutting edges 890, 892 of blade 880 to shear away tissue as blade 880 rotates within outer sheath 900 according to the various methods described above. 906 is formed. In at least one embodiment, the proximal portion 882 of the blade 880 is sized such that a gap is provided between the hollow outer sheath 900 such that suction is applied thereto, for example, by the methods described above. May be. As seen in FIG. 34, when blade 880 rotates arcuate channel 886 (represented by arrow “R”), 886 is at the distal end 884 of blade 880 and the wall of distal sheath tip 901. Tissue is drawn into the interior by suction (represented by arrow “S”) that defines openings 894, 896 between them and applied to the area between the inner wall of the outer sheath 900 and the neck 882 of the blade 800. Make it possible. The blade 880 may rotate clockwise or counterclockwise, or may selectively oscillate between such directions of rotation and still effectively cut tissue that has been drawn inside. . FIG. 34A shows another sheath tip embodiment 901 ′ made from a metallic material, such as, for example, stainless steel with a series of serrated cutting teeth 905 ′ formed on each cutting edge 890 ′, 892 ′. Represents.

  FIG. 35 depicts another blade embodiment 910 that may be substantially the same as the blade 200 except for the differences noted below. In particular, the blade 910 can include a waveguide or proximal portion 912 that terminates in a distal tissue cutting portion 914. The proximal end 912 of the blade 910 can be configured to be screwed or otherwise attached to the ultrasonic horn of any of the various embodiments described above. The distal tissue cutting portion 914 may have opposing channels 916 formed therein that cooperate to define a first cutting edge 920 and a second cutting edge 922. This blade embodiment may be used in connection with any of the various outer sheath configurations described above and is designed to rotate only in a single direction “R” for purposes of tissue cutting. As in the embodiment described above, the arcuate channel 916 defines an opening between the tissue cutting portion 914 of the blade 910 and the inner wall of the distal sheath tip, and between the proximal portion 912 and the inner wall of the outer sheath. Allow tissue to be drawn inside as suction is applied to the area in between.

  FIG. 36 illustrates another surgical instrument 2000, where like numbers used previously to describe the various embodiments above are used to designate similar components. In these embodiments, surgical instrument 2000 includes a housing 302 that houses an ultrasonic transducer assembly 314 attached to an ultrasonic horn 324. In this embodiment, the ultrasonic transducer assembly 314 and the ultrasonic horn 324 may be non-rotatably supported within the housing 302 by known methods. Conductors 151 and 152 may provide an electrical control signal from the ultrasonic generator 12 to the ultrasonic transducer assembly 314. When the ultrasonic generator 12 is activated, the ultrasonic generator assembly 314 applies ultrasonic motion to the ultrasonic horn 324. In this embodiment, the hollow outer sheath 2010 is coupled to an ultrasonic horn 324 for receiving ultrasonic motion from the horn. For example, in various embodiments, the outer sheath 2010 can be coupled to the ultrasonic horn 324 by a screw connection or other suitable fastening configuration.

  This embodiment includes a rotatable blade 2020 that is rotatably supported in an outer sheath 2010 and coupled to a motor 510 that is supported in a housing 302. The motor 510 may include, for example, a stepping motor of the type and configuration described above. The motor 510 may have an encoder associated therewith, which communicates with the control module 24 (FIG. 1) as described above. The blade 2020 can have a hollow distal portion 2022 and a solid proximal portion 2024. See FIG. 36A. The solid proximal portion 2024 may be attached to the motor drive shaft 520 by screws or by another suitable connection. The motor drive shaft 520 can be rotatably supported within the housing 302 by a proximal bearing 342. When a control signal is supplied to the motor 510, the drive shaft 520 rotates about the axis AA, which causes the blade 2020 to rotate about the axis AA within the outer sheath 2010.

  As further seen in FIG. 36A, the hollow outer sheath 2010 is supported within a hollow nosepiece 160 having a suction portion 240 therein. The flexible tube 242 may be attached to a suction port 240 and communicate with a collection container 243 connected to a suction source, generally indicated as 244. The hollow sheath 2010 is disposed on each side of the aspiration port 240 shown in FIG. 36A and has a nose with a proximal seal 2013 and a distal seal 2015 that function to form a fluid tight seal therebetween. It can be supported in the piece 160. The hollow sheath 2010 comprises at least one proximal sheath opening 2014 that is aligned with the suction port 240 between the proximal seal 2013 and the distal seal 2015. In addition, the hollow distal portion 2022 of the blade 2020 is rotatably supported within the hollow sheath 2010 by at least the proximal blade seal 2025 and the distal blade seal 2027. The hollow portion 2022 of the blade 2020 between the proximal blade seal 2025 and the distal blade seal 2027 for at least one blade discharge port 2028 to discharge into the at least one proximal sheath opening 2014. May be provided through.

  In various embodiments, the distal end 2011 of the hollow outer sheath is closed and comprises at least one opening or window 2012 to expose the distal tissue cutting 2025 of the blade 2020. In at least one embodiment, window 2012 includes an elongated slot and the distal tissue cutting portion also includes an elongated slot 2026 in blade 2020 (FIGS. 37 and 38). Thus, suction is applied from the suction source 244 through the port 240, the proximal sheath opening 2014 and the blade discharge port 2028 to the hollow portion of the blade 2020. When the distal openings 2026, 2012 are aligned, tissue “T” can be drawn into the hollow distal portion 2022 of the blade 2020 as shown in FIG. The cut portion of tissue “T” may pass through the hollow distal portion 2022 of blade 2020, exit openings 2028, 2014, and enter collection container 243.

  In use, the clinician may activate the rotating blade 2020 to cut and drain tissue. Upon encountering a bleeding vessel, the clinician activates the ultrasonic transducer assembly 314 to deliver ultrasonic motion to the outer sheath 2010 for hemostatic purposes. For example, spinal fusion surgery requires the removal of disc material due to various disease states. In many cases, this material is hardened and requires considerable force with conventional equipment to disassemble the disk and remove its debris. Once the disc material is removed, the end plate must be scraped to expose the new surface to facilitate the fusion of the plate and cage. The plate must also be shaped to provide a good fit with the type of cage used. Conventional instruments generally require great force by a physician, very close to the critical structure. In other embodiments, the motor may be coupled to rotate the ultrasonic transducer assembly, and the blade may be attached to the ultrasonic transducer assembly as described above, thereby rotating the blade, where Ultrasonic motion can be applied.

  The use of the surgical instrument 2000 described above can be particularly advantageous when performing a discectomy, as shown in FIGS. As can be seen in these figures, the outer sheath 2010 can be inserted into the disk “D”. The rotating blade 2020 can be used to scrape small pieces of the disk and suck them out. These configurations eliminate the need for repeated insertion / removal of surgical tools. The device can be utilized to prepare a vertebral endplate. In the embodiment depicted in FIGS. 41-45, the rotatable cutting blade 2020 has a series of serrated teeth 2021 formed on at least one side of the distal opening 2026 through the opening 2012. It further assists in cutting tissue drawn into the outer sheath 2010. In this embodiment, the retractable safety shield 2040 is movably attached to the outer sheath 2010, and the opening 2012 (FIGS. 43 and 44) is opened from the closed position that substantially covers the opening 2012 of the outer sheath 2010. It is selectively movable to the exposed open position. Such a configuration covers the teeth 2021 of the blade 2020 during insertion and removal of the outer sheath 2010 in the vicinity of critical nerves and other critical tissue. To facilitate movement of the safety sheath 2040 of the outer sheath 2010, a thumb control tab 2042 (FIGS. 41 and 45) is formed on the proximal end of the safety sheath 2040 to allow the clinician to apply a sliding activation force thereto. You may be able to do that. In addition, in various embodiments, a retention protrusion 2044 is formed on the safety sheath 2040 to engage at least one recess or groove 2046 provided in the outer sheath 2010, thereby opening the safety sheath 2040 to a corresponding opening. Or keep it in the closed position. For example, one depression or groove 2046 may correspond to a closed position (safety sheath 2040 includes an opening 2012), and another depression or groove 2046 ′ may correspond to a partially open position. (A portion of the opening 2012 is exposed), another depression or groove 2046 "may correspond to a fully open position (opening 2012 is fully exposed).

  46-51 illustrate a blade 940 having a generally straight distal tissue cutting portion 942. Such a blade configuration provides a potential impedance when the blade 940 is used in an aqueous environment as compared to the impedance and power requirements of various other blade configurations when used in such an environment. Reduction and power increase can occur. That is, such a relatively straighter blade design may require less power for operation in an aqueous environment. The cable 940 may have a round or blunt distal end 944 and a groove 946 that cuts the tissue when the blade 940 is used with the outer sheath 230 as described above. 947, 948 are formed. The groove may have a length “L” of, for example, 2.54 cm (1 inch). The blade 942 may have a suction path 730 of the type and configuration described above. As shown in FIG. 47, a low friction fender or pad 726 of the type and configuration described above may be utilized around the exposed distal end 720 of the outer sheath 230. 48-51 show alternative cross-sectional shapes for blade 940 in which differently shaped grooves 946 are utilized.

  52-55 illustrate another non-limiting blade and sheath embodiment. This embodiment utilizes a hollow outer sheath 950 that can be attached to the nosepiece or ultrasonic transducer assembly of any of the surgical instruments described above by any fastening method or connection configuration. As seen in FIG. 55, the outer sheath 950 has a closed round or blunt nose portion 952 and an elongated rectangular window or opening 954. In one embodiment, for example, the rectangular window 954 has a width “W” of approximately ¼ of the periphery of the hollow outer sheath 950 and a length of approximately 0.25 inches. The sheath 950 may be made of, for example, stainless steel.

  This embodiment also utilizes a blade 960 that may be used in connection with any of the above or other surgical instrument embodiments. For example, the waveguide or proximal portion of the blade may be configured for attachment to the ultrasonic horn or motor drive shaft of the instrument by screws or by another connection. As seen in FIGS. 52-54, the blade 960 has a pair of radially opposed sharpened cutting edges 962 formed at the top that are drawn into the window 954 of the outer sheath 950. In various embodiments that function to cut “T”, the blade 960 may be made of, for example, titanium, with respect to the outer sheath 950, a point that is radially opposed to the inner wall 951 of the outer sheath 950. Sized such that a gap “C” is provided between the leading edge of the cut edge 962. See FIG. 54. In this embodiment, for example, the gap “C” may be approximately 0.0025 inches (0.001 inches). In this embodiment, the blade 960 may be made of, for example, titanium and has a flat distal end 964. In use, tissue “T” is drawn through window 954 when overall rotational motion is applied to blade 960 and suction is applied within hollow outer sheath 950 by any of the various methods described above. , Supplemented between the blade 960 and the inner wall 951 of the outer sheath 950. As described in more detail below, this action separates tissue “T” long enough to cut, for example, when the device is used in an aquatic environment. In some embodiments, the cutting edge 962 can be serrated. In other embodiments, the cutting edge 962 is not serrated.

  FIG. 57 shows another non-limiting blade and sheath embodiment. This embodiment utilizes a hollow outer sheath 970 that can be attached to the nosepiece or ultrasonic transducer assembly of any of the various instruments described above. As shown in FIG. 56, the outer sheath 970 has a round or blunt nose portion 972 and an elongated window or opening 974, which opening is a blade access hole 976 in the nose portion 972, and two radially opposed portions. A lateral window portion 978 is formed. In one embodiment, for example, the outer diameter of the outer sheath 970 can be approximately 0.399 inches (0.157 inches) and the diameter of the blade access holes 976 can be approximately 0.318 inches (0.125 inches). The transverse window portions 978 may each have a width “W” of approximately 0.93 inches and a length “L” of approximately 0.64 inches (0.25 inches). Other window sizes / configurations may be utilized. The sheath 970 may be made of, for example, stainless steel.

  This embodiment is also a waveguide configured for attachment to the ultrasonic horn or motor drive shaft of any of the various surgical instrument embodiments described above by screws or by another suitable connection. Alternatively, a blade 980 having a proximal end is utilized. In various embodiments, the blade 980 can be substantially the same as the blade 960 described above (with a radially opposed sharpened cutting edge 982) provided that the blade 980 is a blade of the outer sheath 970. It has a round / substantially blunt distal tip 984 protruding through access hole 976. See FIG. 57. In various embodiments, the blade 980 may be made of, for example, titanium, between the inner wall 971 of the outer sheath 970 and the tip of the radially opposing sharp cutting edge 962 relative to the outer sheath 970. Is provided with a gap “C”. In some embodiments, for example, the gap may be approximately 0.0025 inches (0.001 inches). In use, tissue “T” is drawn through window portion 978 when overall rotational motion is applied to blade 980 and suction is applied within hollow outer sheath 970 by any of the various methods described above. Rarely is captured between the blade 980 and the inner wall 971 of the outer sheath 970. As described in more detail below, this action separates the tissue long enough to cut, for example when the device is used in an aquatic environment. Also in this embodiment, when the blade 980 is driven by ultrasound, the clinician uses the exposed distal tip 984 for the purpose of spot ablation of fiber tissue or spot coagulation. be able to. In some embodiments, the cutting edge 982 can be serrated. In other embodiments, the cutting edge 982 is not serrated.

  FIG. 59 shows another non-limiting blade and sheath embodiment. This embodiment utilizes a hollow outer sheath 990 that can be attached to the nosepiece or ultrasonic transducer assembly of any of the surgical instruments described above by any fastening method or connection configuration. As seen in FIG. 58, the outer sheath 990 has a closed round or blunt nose portion 992 and an elongated rectangular window or opening 994. In one embodiment, for example, a rectangular window 994 has a width “W” of approximately 0.100 inches and a length of approximately 0.25 inches. The sheath 990 can be made, for example, from a polyamide or similar material that does not cause heating of the blade 1000 from contact therewith. The window 994 may be defined by sharp edges 995, 997. As seen in FIG. 60, the edges 995, 997 may be provided with an angle “B” therebetween. In some embodiments, “B” may be approximately 110 °.

  These embodiments also include a waveguide configured for attachment to the ultrasonic horn or motor drive shaft of any of the above surgical instruments or others by screws or by another suitable connection configuration. A blade 1000 is utilized having a proximal portion. As seen in FIG. 59, the blade 1000 may have a pair of radially opposed sharply cut portions 1002 formed on the top that cut tissue drawn into the window 994 of the outer sheath 990. To function. In various embodiments, the blade 1000 can be made of, for example, titanium. The cutting portion 1002 of the blade 1000 may have a sharp cutting corner 1003 formed at the top. In some embodiments, the cutting corner 1003 can be serrated. In other embodiments, the cutting corner 1003 is not serrated. When the blade 1000 rotates or vibrates back and forth within the outer sheath 990 with respect to the outer sheath 990, the cutting portion 1002 performs a tissue shearing operation between the cutting corner portion 1003 and the sharp edges 995 and 996 of the window opening 994. Can be sized to form. The blade 1000 can be sized relative to the outer sheath 990 to create a slip fit therebetween, which prevents the tissue from being trapped between these two components by another method. The blade 990 can rotate back and forth (arrow "D") or can rotate in a single direction (arrow "E") and can be activated by ultrasound as described above if desired. it can. See FIG. 59. In use, tissue “T” is drawn through window 994 when overall rotational motion is applied to blade 1000 and suction is applied within hollow outer sheath 990 by any of the various methods described above. , Supplemented between the blade 1000 and the inner wall 999 of the outer sheath 990. As described in more detail below, this action separates the tissue long enough to cut, for example when the device is used in an aquatic environment.

  FIG. 62 shows another non-limiting blade and sheath embodiment. This embodiment utilizes a hollow outer sheath 1010 that can be attached to the nosepiece or ultrasonic transducer assembly of any of the surgical instruments described above by any fastening method or connection configuration. As shown in FIG. 61, the outer sheath 1010 may have a closed round or blunt nose portion 1012 and an elongated rectangular window or opening 1014. In one embodiment, for example, the window 1014 has a first imprinted or pressed edge 1016 and a second imprinted or pressed edge 1018 and is approximately 0.100 inches wide. An opening 1019 is defined that may have a “W”. The window 1014 may have a length of approximately 0.25 inches. The sheath 1010 may be manufactured from, for example, stainless steel.

  These embodiments also include a waveguide or proximity configured for attachment to an ultrasonic horn or motor drive shaft of any of the above surgical instruments or others by screws or by another suitable connection. Utilizing a blade 1020 having a central portion. As seen in FIG. 62, the cable 1020 may have a pair of radially opposed sharp cuts 1022, 1024 formed at the top. The blade 1020 may be made, for example, from titanium and has a relatively sharp cutting corner 1025 formed on each cutting portion 1022,1024. In some embodiments, the cutting corner 1025 is serrated. In other embodiments, the cutting corner 1025 is not serrated. The cutting portions 1022 and 1024 form a tissue shearing action between the pressed edges 1016 and 1018 and the cutting corner 1025 when the blade 1020 rotates or vibrates in the outer sheath 1010 with respect to the outer sheath 1010. It can be as big as you want. Such a configuration forms a relatively small local area so as to reduce the problem of contact between the blade and the outer sheath by promoting the tissue cutting effect. In use, when an overall rotational motion is applied to the blade 1020 and suction is applied within the hollow outer sheath 1010 by any of the various methods described above, tissue is drawn through the opening 1019 and the blade Supplemented between 1020 and the inner wall 1011 of the outer sheath 1010. As described in more detail below, this action separates the tissue long enough to cut, for example when the device is used in an aquatic environment.

  FIG. 64 shows another non-limiting blade and sheath embodiment. This embodiment utilizes a hollow outer sheath 1030 that can be attached to the nosepiece or ultrasonic transducer assembly of any of the surgical instruments described above. As shown in FIG. 63, the outer sheath 1030 may have a closed round or blunt nose portion 1032 and an elongated rectangular window or opening 1034. This embodiment may further include a pair of sharp cutting inserts 1036, 1038. The cutting inserts 1036, 1038 may be made from hardened stainless steel, for example, and may be attached within the hollow sheath 1030, for example, by welding. The window 1034 has a width “W” of approximately 0.154 inches and a length of approximately 0.25 inches. The sheath 1030 may be manufactured from, for example, stainless steel.

  These embodiments are also configured for attachment to the ultrasonic horn or motor drive shaft of any of the surgical instruments or other described herein by screws or by another suitable connection. A blade 1040 is utilized having a waveguide or proximal portion. As seen in FIG. 64, the blade 1040 has a pair of radially opposed cuts 1042 formed at the top, which has a relatively sharp cut corner 1043. In some embodiments, the cutting corner 1043 can be serrated. In other embodiments, the cutting corner 1043 is not serrated. In various embodiments, the blade 1040 may be made of, for example, titanium, with a sharp cutting corner 1043 as the blade 1020 rotates or vibrates within the hollow outer sheath 1030 relative to the cutting insert 1036, 1038. And may be sized so as to form a tissue shearing action between the cut and the cut 1042. In order to provide clearance for blade 1040 during operation, the outer diameter of blade 1020 is smaller than the inner diameter of outer sheath 1030. Contact occurs only between the cutting portion 1042 of the blade 1040 and the insertion portions 1036, 1038 along the window opening 1034, and the tissue is drawn by suction.

  FIG. 66 shows another non-limiting blade and sheath embodiment. This embodiment utilizes a hollow outer sheath 1110 that can be attached to the nosepiece or ultrasonic transducer assembly of any of the surgical instruments described above by any fastening method or connection configuration. As shown in FIG. 65, the outer sheath 1110 may have a closed round or blunt nose portion 1112 and an elongated rectangular window or opening 1114. In this embodiment, the lateral edges 1116, 1118 of the window 1114 are coined or pressed inward. Window 1014 has a width “W” of approximately 0.10 inches and a length of approximately 0.25 inches.

  These embodiments also include a waveguide configured for attachment to the ultrasonic horn or motor drive shaft of any of the above surgical instrument embodiments or others by screws or by another suitable connection configuration. A blade 1120 is utilized having a tube or proximal portion. As seen in FIG. 66, the blade 1120 has a pair of radially opposed cuts 1122 formed at the top, which has a relatively sharp cut corner 1023. In some embodiments, the cutting corner 1023 can be serrated. In other embodiments, the cutting corner 1023 is not serrated. In various embodiments, the blade 1020 may be made of, for example, titanium, and between the sharp cut corner 1023 and the cut 1122 as the blade 1120 rotates or vibrates relative to the pressing edges 1116, 1118. May be sized to create a tissue shearing action. Such a configuration defines a larger gap C <b> 1 between the cutting portion 1122 of the blade 1120 and the inner wall 1111 of the sheath 1110. A gap C2 that is smaller than C1 is provided to form a tissue shearing motion between the lateral edges 1116, 1118 and the cut 1122.

  Figures 67-69 show another non-limiting blade and sheath embodiment. This embodiment utilizes a hollow outer sheath 1210 that can be attached to the nosepiece or ultrasonic transducer assembly of any of the surgical instruments described above. The hollow outer sheath 1210 has a distal nose portion 1212 that includes an upper opening 1214 and a lower opening 1215 that function to define arcuate lateral sides 1216, 1218. The distal nose portion 1212 may further have a closed end 1219 that extends between the lateral sides 1216, 1218.

  This embodiment further includes a blade 1220, which has a waveguide or proximal end configured to be attached to the ultrasonic transducer assembly of any of the surgical instruments described above. The blade 1220 further has a distal end 1221, which has a cavity 1222, which is a pair of arcuate cuts 1224 that extend over the arcuate lateral sides 1216, 1218 of the hollow sheath 1210. , 1226. One or both of the cutting portions 1224, 1226 may have serrated teeth 1227, or neither. In the embodiment shown in FIG. 67, the cavity 1222 has a cross-sectional shape that is approximately similar to the flat bottom “C”. However, the cavity 1222 can have other cross-sectional shapes. At least one suction path 1230 may be provided through the blade 1220 as shown. The suction path may be in communication with a suction source (not shown).

  In various embodiments, the blade 1220 may be made of, for example, titanium, with the bottom 1232 of the blade 1220 relative to the distal nose portion 1212 of the hollow sheath 1210 and the lateral side 1216 of the nose portion 1212. , 1218 and extending downwards. Similarly, the cut edges of arcuate sides 1224, 1226 extend beyond lateral sides 1216, 1218, as shown in FIG. While the exposed bottom 1232 of the blade 1220 is used to coagulate tissue, the cutting edges 1224, 1226 can be used to cut and excise the tissue.

  As shown in FIG. 70, the proximal end 1211 of the hollow sheath 1210 protrudes from the handle housing 1240. As described above, the handle housing 1240 houses the ultrasonic transducer assembly, motor, and slip ring assembly and is coupled to the control system 10. The handle housing 1240 may include a selection switch 1241 that allows the clinician to select between a first “ultrasound” mode 1242, a second “shaver” mode 1244, and a third “infusion” mode 1246. Make it possible to do. The conversion mechanism 1241 communicates with the control system 10 and automatically directs the blade 1220 in the desired direction of rotation. For example, to utilize the device 1200 in the ultrasound mode 1242, the clinician switches the selection switch 1241 to the ultrasound mode position 1242 (shown as operation 1250 in FIG. 71). When in the first ultrasonic configuration 1242, the motor rotates the blade 1220 to the position shown in FIGS. 67 and 68 (shown as action 1252 in FIG. 71), and then stops it in this position to make it hollow. The bottom 1232 of the blade 1220 is exposed through the sheath 1210 (shown as action 1254 in FIG. 71). When in this position, the ultrasound transducer assembly is activated to allow the bottom 1232 to be used to achieve hemostasis (shown as action 1257 in FIG. 71). More specifically, when in the ultrasound mode 1242, the clinician may orient the bottom 1232 against the bleeding tissue and then apply strong pressure to the tissue by the exposed portion 1232 of the blade 1220 ( 71, shown as action 1256). The clinician then activates the ultrasound transducer assembly to achieve hemostasis (shown as action 1258 in FIG. 71). In another embodiment, the device 1200 may comprise a series of switches / buttons as described above, which communicate with the control system so that rotation can be initiated with the activation of one switch. Activation of another switch may initiate rotational vibration, and activation of another switch cooperates with the control system to rotate the blade to the ultrasonic position and stop it, and then activate the ultrasonic transducer assembly. In still other embodiments, the ultrasonic transducer assembly may be activated by yet another separate switch. All such alternative configurations are within the scope of the various non-limiting embodiments disclosed herein and their corresponding equivalent structures.

  FIG. 72 illustrates the use of the device 1200 when in the shaver mode 1244. In particular, the selection switch 1241 is moved to the shaver position 1242 (shown as action 1260 in FIG. 72). When in this position, the motor continuously rotates the blade 1220 within the hollow outer sheath 1210 (shown as action 1262 in FIG. 72). In other embodiments, the motor may cause the blade 1220 to oscillate back and forth within the outer sheath 1210, or in other embodiments, the selection switch can be moved to yet another position where rotational oscillation is initiated. It may be. In either case, the clinician may then contact the tissue with a rotating or vibrating blade (1220), whereby the tissue may be scraped and drained through the suction path 1230 (shown as action 1264 in FIG. 72). .

  FIG. 73 illustrates the use of the device 1200 when in the infusion mode 1246. In particular, the selection switch 1241 is moved to the injection position 1246 (shown as operation 1270 in FIG. 73). In this position, the blade 1220 is maintained in a stopped position (shown as action 1272 in FIG. 73). The clinician may then direct the blade to the desired position and then inject the desired drug (shown as action 1274 in FIG. 73). One form of drug that can be injected may include, for example, a cell-generating drug sold under the trade name “Carticel”. However, other drugs and agents can be utilized. The infusion action directs the blade 1220 to a position within the outer sheath 1210 such that a drug path 1284 extending through the blade 1220 is exposed through the outer sheath 1210 to allow the drug to be advantageously applied to adjacent sites. Can be achieved. The medication can then be infused by activating a pump 1280 that is in communication with the medication source 1282. See FIG. In various embodiments, the device 1200 may have an infusion trigger 1249 in communication with the pump 1280 such that upon activation of the infusion trigger 1249, the pump 1280 releases the drug through the pathway 1284 (FIG. 68). In another embodiment, the drug can be manually injected into a port (not shown) in communication with the drug path 1284 in the blade 1220, for example, by a syringe.

  FIGS. 74-77 illustrate another non-limiting surgical instrument embodiment 1300. The device 1300 may include any one of the handpiece devices 300, 400, 500 described above. For example, the device 1300 may include a hand piece 300 that incorporates the following differences. Handpiece 300 includes blade 200, which has a waveguide or proximal end that is coupled to an ultrasonic transducer assembly that applies ultrasonic motion to blade 200 when activated. To do. The blade 200 can also be rotated by a motor configuration housed within the handpiece 300 as described above. Blade 200 may extend through inner sheath 1320, which protrudes from handpiece 300. Blade 200 can freely and selectively vibrate and rotate within inner sheath 1320. One or more sealing members 1322 may be provided between the blade 200 and the inner sheath 1320 to prevent fluid and tissue from entering between the inner sheath 1320 and the blade 200. The sealing member 1322 can be made of, for example, silastic silicone.

  The device 1300 may further include an outer sheath 1330 that is movably received over the inner sheath 1320. The outer sheath 1330 can be sized such that the suction tube 1350 can extend between a portion of the inner sheath 1320 and a portion of the outer sheath 1330 relative to the inner sheath 1320. Suction tube 1350 may be in communication with a suction source, generally designated 1352. See FIG. 74. As seen in FIGS. 74-77, the outer sheath 1330 can include a swing arm portion 1332 that protrudes distally from the distal end 1331 of the outer sheath 1330. The swing arm 1332 may be relatively straight (FIG. 75) or it may have a slightly curved distal end 1334 (FIG. 76). As seen in FIG. 76, the distal end 1334 may have a sharp cutting surface 1336 at the top. As can also be seen in FIGS. 74-76, in some embodiments, the blade 200 may have a curved blade tip 1360 having a pair of lateral cutting edges 1362 formed thereon. . In other embodiments, the blade tip 1360 may be straight. In some embodiments, the blade 200 can be rotated by the various methods described above. In other embodiments, the blade 200 may not rotate. In such embodiments, for example, the clinician may choose not to start the motor so as not to rotate the blade, or the handpiece includes a handpiece that does not include a motor for rotating the blade. obtain.

  In use, the swing arm portion 1332 may cover a portion of the distal end 1360 of the blade 200. In one mode of use, the outer sheath 1330 is maintained in a position such that the swing arm portion 1332 covers the back side of the blade 200, as shown in FIG. Such a configuration leaves the curved blade tip 1360 exposed. When in this position, for example, the curved blade tip 1360 can be utilized to excise tissue such as a meniscus. In the second mode of operation, the swing arm 1332 is moving.

  In the embodiment shown in FIGS. 74-77, the suction tube 1350 is utilized to pull the loose tissue toward the blade tip 1360 and also remove small pieces of tissue excised during cutting. . In other embodiments, suction can occur in the annular space between the sheaths 1320 and 1330. In yet other embodiments, the blade 200 may have a suction path (not shown) extending therein, which ultimately communicates with a suction source, as described above. Such a suction path probably exits the blade 200 at the proximal end node. In yet other embodiments, suction is not utilized.

  In some embodiments, the swing arm portion 1332 may be permanently maintained in a position that contacts the blade 200. In still other embodiments, a lubrication or low friction pad (not shown) may be attached to the swingarm position 1332 so that the pad contacts the blade 200. In other embodiments, a gap of 0.005 cm to 0.025 cm (0.002 ″ to 0.010 ″) may be provided between the swing arm portion 1332 and the blade 200. In other embodiments, the swing arm portion 1332 extends around the length of the curved portion of the blade 200 so that the entire blade 200 is covered from the back side.

  The various non-limiting embodiments described above can be effectively utilized in connection with a variety of different surgical applications and are particularly suitable for cutting and coagulating tissue in an aqueous environment for arthroscopic surgery. is there. However, in such applications, if fluid passes between the blade or waveguide and the inner sheath, the fluid may enter the housing and damage the internal components. Various sealing configurations are known for use with ultrasonically driven surgical instruments. For example, US Pat. Nos. 5,935,144 and 5,944,737 (the disclosures of each of which are incorporated herein by reference in their entirety) are respectively laparoscopic and open surgery. Various sealing configurations are disclosed for use of ultrasonic surgical instruments in a conventional environment (ie, a non-aqueous environment). However, the various non-limiting embodiments described below utilize an improved sealing configuration that may be more suitable for use in an aquatic environment.

  More specifically, referring to FIG. 78, an ultrasound device 1400 is shown that includes a housing 1402 that rotatably supports an ultrasound transducer assembly 1404 therein. For example, the ultrasonic transducer assembly 1404 can be rotatably supported within the housing 1402 by a series of bearings (not shown). The ultrasonic horn 1406 may be coupled to the ultrasonic transducer assembly 1404 and the ultrasonic tool 1410 is attached thereto by conventional means, which may typically include a threaded configuration. As used herein, the term “ultrasonic tool” may include any one of the blades and cutting members described herein. The portion of the ultrasonic tool 1410 that is coupled to the ultrasonic horn 1406 may be referred to as a waveguide portion 1412. The waveguide 1412 may include an integral part of the ultrasonic tool 1410 or it may include a separate component attached thereto, for example with a screw connection. In the embodiment shown in FIG. 78, the ultrasonic instrument 1410 extends through a hollow outer sheath 1420. The distal end of the outer sheath 1420 and the ultrasonic instrument 1410 may be configured with any one of the various blade and sheath configurations described above, in addition to the above.

  As seen in FIG. 78, the proximal shaft 1430 is attached to the ultrasonic transducer assembly 1404. A drive gear 1432 is mounted on the proximal shaft 1430 that meshes with a drive gear 1434 coupled to the output shaft 1436 of the motor 1440. Ultrasonic electrical signals and motor control signals may be provided from the control system 10 through a slip ring assembly 1450 of the type and configuration described above. The device 1400 may further include the various control button configurations described above so that the device can be used in an ultrasonic mode, a non-ultrasonic mode (eg, a rotational shaving mode) and combinations of these modes. Unlike the various instruments described above, the motor 1440 is not coaxially aligned with the ultrasonic transducer assembly.

  FIG. 79 illustrates a non-limiting embodiment of a sealing assembly 1470 that can be utilized between the waveguide or proximal portion 1412 of the ultrasound instrument 1410 and the outer sheath 1420. The seal 1470 may be made of silicon or other material such as Ultem® and may be overmolded into the waveguide 1412 or otherwise sealed at node “N”. Including an annular member attached thereto. The sealing portion 1470 extends in the shape of an axis in the opposite axial direction beyond the first annular sealing portion 1472 and the first annular sealing portion 1472 formed on the waveguide 1412 at the node “N”. And second axial seals 1474, 1476 separated by grooves 1478. The groove 1478 may allow the two axial seals 1474, 1476 to bend slightly relative to each other in sealing contact with the outer sheath 1420. The narrower first annular seal 1472 may avoid excessive heat buildup while providing a larger contact area in contact of the seal 1470 to the outer sheath 1420.

  FIG. 80 illustrates a non-limiting embodiment of a seal 1480 that can be utilized between the waveguide or proximal portion 1412 of the ultrasound instrument 1410 and the outer sheath 1420. The seal 1480 may be made of silicon or other material such as Ultem® and may be overmolded into the waveguide 1412 or otherwise sealed at node “N”. Including an annular member attached thereto. Seal 1480 may be configured to be adjacent to an inwardly extending annular adjacent ring 1490 formed on outer sheath 1420. Seal 1480 is located distally relative to adjacent ring 1490. As fluid pressure accumulates in the outer sheath 1420, the seal 1480 is driven into the adjacent ring 1490, thereby increasing the strength of the seal. The outer sheath 1420 may be made from stainless steel, for example.

  FIG. 81 illustrates a non-limiting embodiment of a seal 1500 that can be utilized between the waveguide 1412 of the blade 1410 and the outer sheath 1420. The seal 1500 may be made of silicon or other material such as Ultem® and may be overmolded into the waveguide 1412 at node “N” or otherwise sealed. Including an annular member attached thereto. The seal 1480 can be configured to be received within an annular groove 1423 provided in the outer sheath 1420. The outer sheath 1420 may be made from stainless steel, for example.

  FIG. 82 illustrates a non-limiting embodiment of a seal 1510 that can be utilized between the waveguide or proximal portion 1412 of the ultrasound instrument 1410 and the outer sheath 1420. The seal 1510 may be made of silicon or other material such as Ultem®, for example, overmolded into the waveguide portion 1412 at node “N” or otherwise sealed. An annular member that is attached while The sealing portion 1510 includes an inner rim portion 1512 formed on the waveguide 1412 at the node “N”, and extends axially in the opposite direction beyond the inner rim portion 1512 and is separated by the groove 1518. May have axial seals 1514, 1516. Axial portions 1514, 1516 are sized to extend into groove 1520 provided in outer sheath 1420. As can be seen in FIG. 82, the groove 1520 has a ring 1522 protruding inward and sized to extend into the groove 1518 of the seal 1510. In the illustrated embodiment, the ring 1522 has a ramp 1524 formed in the top that allows the seal 1510 to slide over it during assembly and then lock in place. The outer sheath 1420 may be made from, for example, Ultem®.

  83 and 84 illustrate a non-limiting embodiment of a seal 1530 that can be utilized between the waveguide or proximal portion 1412 of the ultrasound instrument 1410 and the outer sheath 1420. The seal 1530 may be made of silicon or other material such as Ultem®, for example, overmolded into the waveguide 1412 at node “N” or otherwise sealed. Including an annular member attached thereto. The sealing part 1530 may have a groove 1532 as shown in FIG. The outer sheath 1420 is then pleated, thereby breaking the seal 1530 as shown in FIG. The outer sheath 1420 can be pleated evenly around the entire periphery, or it can be pleated at a separate location. For example, four evenly spaced (eg, 90 ° spaced) pleats may be utilized. In such embodiments, the outer sheath 1420 can be made from, for example, stainless steel.

  FIG. 85 shows a proximal axial portion 1542 and a distal axial section 1544 adapted to be interconnected together, for example, by welding, press fitting, screwing, or snapping together. A portion of the outer sheath 1540 is shown. As seen in FIG. 85, the distal axial section 1544 is inserted into the waveguide or proximal portion 1412 of the ultrasound tool 1410 at node “N” while overmolding or otherwise sealing. A groove portion 1546 sized to engage with a part of the annular sealing portion 1550 is provided. Thus, when attached to each other, the proximal axial section 1542 and the distal axial section 1544 function to supplement and compress a portion of the seal 1550 therebetween. In another embodiment, the groove portion 1546 may be provided in the proximal axial section 1542, or each section 1542, 1544 cooperates with the inner annular seal 1550 to accommodate the groove section therein. Can have.

  FIG. 86 shows a portion of the outer sheath, generally designated 1560, that consists of two lateral halves 1562, 1564. FIG. Each lateral half 1562, 1564 has a semi-annular groove section 1566 formed therein. See FIG. 87. When the transverse halves 1562, 1564 are joined together to form a hollow outer sheath 1560, the semi-annular groove section 1566 is overmolded or otherwise attached to the waveguide or proximal portion 1412. An annular groove 1568 sized to receive the annular seal 1570 formed is formed. By creating a two-piece outer sheath 1560, the seal 1570 has a sheath 1560 and more generally than the waveguide 1412 would have to be pressed down against the outer sheath 1560 during the assembly process. Can have much higher interference. The two outer sheath halves 1562, 1564 may be joined together by welding, snap-fit, or other suitable method. Accordingly, the seal 1570 can be initially incorporated into the waveguide 1412. The two halves 1562, 1564 may then be brought together around the waveguide 1412 so that the seal 1570 is captured in the groove 1568. The halves 1562, 1564 are then fastened together in this position.

  FIG. 88 illustrates a non-limiting embodiment of a seal 1580 that may be utilized between the ultrasound device waveguide 1412 and the outer sheath 1420. The seal 1580 can be made of silicon or other material, such as Ultem®, and is overmolded to the waveguide or proximal portion 1412 at node “N” or otherwise. Including an annular member attached while being sealed. Seal 1580 may be held in place by proximal ring 1590 and distal ring 1592. Proximal ring 1590 may include any portion of outer sheath 1420, or it may include a separate component that may or may not be pressed against outer sheath 1420. The distal ring 1592 may be glued, pressure fitted, or otherwise attached to the outer sheath 1420. Upon introduction, the distal ring 1592 can provide compression on the seal 1580. This increases the stress between the seal 1580 and the waveguide 1412 and further reduces fluid movement beyond the seal 1580. The rings 1590, 1592 may include a split annular ring or a ring that does not have a split portion therein. In addition, as seen in FIG. 88, the rings 1590, 1592 can be sized such that a constant gap “C” is provided therebetween for the waveguide 1412.

  FIG. 89 illustrates a non-limiting embodiment of a seal 1600 that can be utilized between the waveguide or proximal portion 1412 of the ultrasound instrument 1410 and the outer sheath 1420. The seal 1600 may be made of silicon or other material such as Ultem®, for example, overmolded into the waveguide 1412 at node “N” or otherwise sealed. Including an annular member attached thereto. Seal 1600 may have an outer diameter that is larger than the inner diameter of outer sheath 1420. Seal 1600 may further include a proximal side 1602 and a distal side 1604. When assembled, the exterior of the proximal side 1602 of the seal 1600 contacts the inner wall 1421 of the outer sheath 1420 while sealing. Thus, if fluid pressure “P” accumulates at the distal side of the seal 1600, the seal 1600 is further promoted into sealing contact with the outer sheath 1420, thereby causing the waveguide 1412 and the outer sheath to Produces a good seal between 1420.

  FIG. 90 illustrates a non-limiting embodiment of a seal 1610 that can be utilized between the waveguide or proximal portion 1412 of the blade and the outer sheath 1420. The seal 1610 may be made of silicon or other material, such as Ultem®, and includes an annular member that is overmolded to the outer sheath 1420 or attached while sealing otherwise. . In this embodiment, an annular groove 1620 can be provided in the waveguide 1412 to receive a portion of the seal 1610 therein. In another embodiment, no groove is provided. 79-82 are illustrated cutting blades without departing from the spirit and scope of the various non-limiting embodiments disclosed herein, and their corresponding equivalents. It is further understood that instead of the waveguide or proximal portion of the device, it may be similarly attached to the outer sheath. In addition, it is further understood that the various sealing embodiments described herein can be effectively utilized with any of the surgical instrument embodiments described above. That is, the various non-limiting sealing configurations disclosed herein, and their corresponding equivalent structures, provide a seal between the ultrasonic blade or waveguide and the corresponding inner sheath. It can be used effectively to achieve. In embodiments that utilize an inner sheath and an outer sheath, but do not apply suction therebetween, the various non-limiting sealing configurations disclosed herein, and their corresponding equivalents, are also included in the inner sheath. Can be effectively utilized to achieve a substantially fluid tight seal between the outer sheath and the outer sheath. In yet another non-limiting embodiment, a seal is utilized between the ultrasonic blade and the outer sheath, and the ultrasonic blade does not engage the full rotational movement relative to the outer sheath. In such embodiments, the seal may be securely attached to the ultrasonic blade and other sheaths. In yet other non-limiting embodiments, the ultrasonic blade may vibrate within the outer sheath. For example, an ultrasonic blade can oscillate through a 90 ° arc (45 ° on both sides of the central axis). In such an embodiment, the seal can be securely attached to the outer sheath and the ultrasonic blade, for example, by adhesive, crimping, or the like. The sealing material may include an elastic rubber material or the like that conforms to the twist of the seal in the range of ± 45 °. In such embodiments, the extension experienced by the seal can assist in returning the blade to the 0 ° neutral position (alignment with the central axis).

  Various above-described embodiments utilize rotating blades that function to shear tissue between the cutting edge formed on the blade and the edge of the surrounding outer sheath. Such a configuration is very effective for cutting most tissues, but it can be difficult to cut hard tissue, such as tendon tissue effectively, between the blade and the outer sheath. Because this can tend to “milk”. Such problems are similar to problems found when scissors are used, for example, to cut hard materials such as skin. That is, the scissors blade separates and the material is not cut. This phenomenon is illustrated graphically in FIGS. As seen in these figures, cutting blade 1700 is utilized to cut hard tissue “T”. Moving inward toward the blade 1700 tissue “T”, the tissue “T” moves between the blades 1700, thus separating them.

  In various blade and sheath embodiments disclosed herein, it may be advantageous to minimize the amount of clearance between the outer sheath cut and the blade cutting edge. For example, it is desirable to maintain the amount of clearance between the outer sheath cutting edge and the blade cutting edge within a range of 0.0025 cm (0.001 ″) to 0.013 cm (0.005 ″). There is a case. In other non-limiting embodiments, one cutting edge or portion is harder than the other cutting portion. For example, the cutting edge of the blade may be stiffer than the cutting of the outer sheath, or vice versa. The motor can then be activated with or without ultrasound to achieve a near-zero gap between the cutting edges / portions. In addition to or in lieu of such an approach, other embodiments bias at least the distal end of the blade into an “off-center” configuration within the outer sheath while still remaining internal. A configuration that facilitates rotation of the blades may be utilized. More specifically and with reference to FIGS. 92-93, a blade 200 of the type and configuration described above is shown extending through the outer sheath assembly 3000. In the illustrated embodiment, the outer sheath assembly 3000 is used in conjunction with a surgical instrument 3001, which selectively applies full rotational motion to the blade 200 and selectively applies ultrasonic motion thereto. To do so, it can be configured by any of the methods described above.

  In the embodiment shown in FIG. 93, the blade 200 extends axially through an inner sheath 3020 that is mounted within a portion of the instrument housing 3010. The outer sheath assembly 3000 is attached to the instrument housing 3010 and has a distal tip 3002 having a window or opening 3004 therein. As described above, the window 3004 allows it to be retracted into the tip cavity 3006 formed in the distal tip 3002. Suction can be applied to the tip cavity 3006 through the suction port 3007 of the distal tip 3002 of the outer sheath assembly 3000 in communication with the suction source 244. In these embodiments, the blade 200 is somewhat flexible and can be made of, for example, titanium. In addition, the waveguide or proximal portion of blade 200 extends through bushing 3030 that is mounted within inner sheath 3020 at the location of node “N”. In various embodiments, the inner sheath 3020 can be made of a material that is substantially rigid and resists bending. For example, the inner sheath 3020 can be made from Ultem or similar material. The bushing 3030 is made of, for example, Ultem (registered trademark), and may be nonrotatably held in the inner sheath 3020 by, for example, stainless steel.

  As seen in FIGS. 92A and 93, the waveguide or proximal end portion 701 of the blade 200 extends through a hole 3032 in the bushing 3030. The center line CL-CL of the bushing hole 3032 is offset from (ie, not coaxial with) the central axis AA defined by the outer sheath 3000. The bushing hole 3032 is such that the proximal portion 701 is free to rotate inside relative to the proximal end portion 701 of the blade 200 to offset the distal end 700 of the blade 200 from the central axis AA of the outer sheath 3000. Sized to function to bias, whereby the tissue cutting distal end 705 of the blade 200 is maintained in rotational contact with the cutting edge 3005 defined by the window opening 3004. . In some embodiments, for example, the blade 200 may be biased from the center by a distance that may be as large as 0.030 ″. The tissue cutting distal end 705 of the blade 200 may be Being biased in this manner, the distal end 705 resists the forces that occur when cutting hard tissue (this would otherwise cause the cutting edge 706 of the distal end 705 to be moved into the window opening 3004). Can be moved away from the cutting edge 3005).

  94 and 95 illustrate another embodiment, where the proximal portion 701 of the blade 200 can be made from, for example, silastic silicone or Ultem® and held within the inner sheath 3020 by, for example, a slip fit. , Extends coaxially through the bushing 3040. In connection with the above embodiment, bushing 3040 may be located at node “N” along the waveguide or proximal portion of blade 200. However, in this embodiment, the distal portion 711 (ie, the portion of the blade 200 that extends distally from the bushing 3040) is slightly bent so that the tissue cutting distal end 705 of the blade 200 is cut into the window opening 3004. Energize to the edge 3005. For example, the distal portion 711 of the blade 200 may bend so that it is off center (distance OS in FIG. 95) by approximately 0.030 inches. With such a configuration, the tissue cutting distal end 705 of the blade 200 resists forces in cutting hard tissue (this would otherwise cause the cutting edge 706 of the blade 200 to move away from the cutting edge of the window opening 3004). Can be moved away from part 3005).

  FIGS. 96-97 illustrate another non-limiting outer sheath 3040 and blade 200 embodiment. In this embodiment, a distal outer sheath tip 3050 is utilized. The distal outer sheath tip 3050 may be made of a metal such as, for example, stainless steel and has a proximal bearing portion 3052 that extends to the open distal end 3062 of the outer sheath 3060. The outer sheath 3060 may be made from stainless steel, for example, and may be attached to the distal outer sheath tip 3050 by fasteners, adhesives, and the like. The proximal end 3062 of the outer sheath 3060 is attached to a portion of the instrument housing as described above. The instrument may include many of the various instrument embodiments detailed above, which provide full rotational movement to the blade 200 and in addition ultrasonic movement thereto.

  A waveguide or proximal portion 701 of blade 200 is attached to an ultrasonic horn (not shown) and extends through inner sheath 3070 in various ways as described above. Proximal portion 701 of blade 200 may be rotatably supported within inner sheath 3070 by bushing 3040 as described above. The distal portion 711 of the blade 200 extends rotatably through a lumen 3054 in the distal outer sheath tip 3050. See FIG. 97. A window 3056 is formed in the distal outer sheath tip 3050 to expose the tissue cutting distal end 705 of the blade 200. As in the various embodiments described above, the window 3056 may define at least one cutting edge 3057 that is retracted into the window 3056 across the rotating tissue cutting distal end 705 of the blade 200. Cut the tissue. In this embodiment, the outer diameter “OD” of the cut distal end portion 705 of the blade 200 at the point where the distal end 705 of the blade 200 projects distally into the window opening 3056 is the inner diameter “ID” of the lumen 3054. Is bigger than In some embodiments, for example, the internal lumen diameter “ID” may be approximately 0.356 cm (0.140 ″) and the blade “OD” is approximately 0.381 cm ″ (0.150 ″). May be. Such a configuration causes interference between the tissue cutting distal end 705 of the blade 200 and the distal outer sheath tip 3050. In such a configuration, the distal portion 711 of the blade 200 essentially comprises a cantilevered beam so that the tissue cutting distal end 705 of the blade 200 is lowered by the distal outer sheath tip 3050 (FIG. 97). ) Pressed.

  In the embodiment shown in FIGS. 92-97, it may be desirable to provide a certain amount of clearance between the distal end 3058 of the distal outer sheath tip 3050 and the curved tip 702 of the blade 200. . This gap “C” is illustrated in FIG. Such a gap allows unobstructed ultrasonic movement of the blade 200. However, it may be desirable to minimize such a gap “C” in order to reduce suction loss around the curved tip 702, which can hinder the ability of the device to cut tissue.

  Also, aspiration must be applied in the various ways described above from the aspiration source (not shown) within the distal outer sheath tip 3050 to facilitate the retraction of tissue into the window opening 3056. As shown in FIGS. 97 and 98, in various embodiments, for example, a suction path 3080 is provided in the distal outer sheath tip 3050. The seal 3090 is pivoted to the distal portion 711 of the blade 200 to form a fluid tight seal at the point where the distal portion 711 of the blade 200 exits the inner sheath 3070. See FIG. 97. Also in this embodiment, the distal end 3072 of the inner sheath 2070 extends into an opening 3055 in the bearing portion 3052 of the distal outer sheath tip 3050 to provide relative positive support thereto. As seen in FIG. 98, the suction path 3080 forms a break in the inner sheath support surface 3057 defined by the opening 3055. FIG. 99 shows another distal outer sheath tip 3050 ′, where the suction path 3080 ′ extends into an opening 3055 ′ that supports the distal end 3072 of the inner sheath 3070.

  Various ultrasonic surgical instruments that utilize an outer sheath and rotatable cutting member configuration also face the problem of deformation of the outer sheath and blades due to the thermal and high contact forces between these two components. To do. Deformation of the distal tip of the outer sheath can be reduced by changing the tip material to metal, but this can have the undesirable effect of blade damage due to abrasion, which is ultimately Can cause blade breakage and very short blade life. Such damage due to abrasion of the sheath tip blade can be caused by metal tube contact between the blade and the sheath tip. This condition can be exacerbated when cutting hard tissue such as tendons. As described above, such hard tissue urges the cutting edges away from each other, causing the opposite cutting edge or surface of the blade to contact the sheath tip, thereby causing wear.

  Various non-limiting embodiments described herein, and their corresponding equivalents, are thin friction reducing materials that reduce material on the inner wall of the tip cavity formed in the distal tip of the outer sheath. Or, in another embodiment, a low friction or friction reducing pad may be mounted within the tip cavity to protect the blade. One representative embodiment is shown in FIGS. As seen in these figures, the outer sheath 900 'described above has a friction reducing polymer coating or pad 3100 therein. In various embodiments, the distal tip 902 ′ of the sheath 900 ′ may be made from a metal such as stainless steel, and the friction reducing material or pad 3100 may be, for example, polyimide, carbon-filled polyimide, Teflon®. ), Teflon-Ceramic, etc. In embodiments where a pad is utilized, the pad may be mounted within the tip 902 ', for example, by an adhesive or dovetail configuration. Pad 3100 is preferably configured to conform to the corresponding shape of the blade. For example, as shown in FIG. 101, a blade 3110, which may be substantially similar to the blade 200 described above, has a distal end 3112 that separates two cutting surfaces 3116, 3118. Have The cutting surfaces 3116, 3118 have an arcuate shape and have a cutting edge 3120 formed on each edge thereof. In this embodiment, the polymer pad 3100 also has an upper surface 3101 having a similar arcuate shape. The advantage of this concept is that it maintains a hard metal cutting edge (eg, stainless steel), which is advantageous for cutting hard tissue. If the pad 3100 is made from a more flexible material that can otherwise support the force applied to the blade, this also protects the wide cutting surfaces 3116, 3118 of the blade 200. In addition or alternatively, the inner wall 903 'of the tip 902' may be coated with a friction reducing coating 3130 of the type described above. The coating 3130 may include a separate component that is held in place by an adhesive, or it may include a deposited coating that adheres directly to the inner surface 903 'of the tip 902'. For example, Teflon® material can be applied to the portion of the inner wall 903 'through vapor deposition. The portion of tip 902 'that does not require coating may be masked by known masking techniques prior to exposing tip 902' to the deposition process.

  FIG. 102 shows a tissue cutting blade end 3112 'that can be coated with a relatively hard, low friction material to increase surface hardness and reduce friction. In particular, as seen in this figure, at least a portion of the cutting surface 3116 ′, 3118 ′ is coated with a coating material 3130. In some embodiments, for example, the coating material may include a coating material such as, for example, titanium nitride, diamond-like coating, chromium nitride, graphite iC ™. To avoid blade wear and eventual blade failure, blade 3060 'can be utilized in conjunction with an outer sheath tip made of metal (eg, stainless steel). In another embodiment, the entire distal tissue cutting end of the blade may be coated with a coating material 3130.

  The devices described herein can be designed to be discarded after a single use, or they can be designed to be used multiple times. In either case, however, the device can be reconditioned for reuse after at least one use. Reconditioning can include any combination of device disassembly steps, subsequent cleaning steps, or replacement of specific parts, and subsequent reassembly steps. In particular, the device can be disassembled and any number of parts or components of the device can be selectively replaced or removed in any combination. Upon cleaning and / or replacement of particular components, the device can be reassembled for subsequent use upon functional realignment or by the surgical team immediately prior to surgery. One skilled in the art will appreciate that various techniques for disassembly, cleaning / replacement, and reassembly can be used to recondition the device. The use of such techniques, and the resulting reconditioned device, are all within the scope of this application.

  Preferably, the various embodiments described herein have been processed before surgery. First, a new or used instrument is obtained and cleaned as necessary. The instrument can then be sterilized. In one sterilization method, the instrument is placed in a closed and sealed container, such as a plastic or TYVEK bag. The container and instrument are then placed in a field of radiation that can penetrate the container, such as gamma rays, x-rays, or high energy electrons. This radiation kills bacteria on the instrument and in the container. The sterilized instrument can then be stored in a sterile container. The sealed container keeps the instrument sterile until it is opened in the medical facility. Sterilization can also be performed by any number of methods known to those skilled in the art including beta or gamma radiation, ethylene oxide, and / or steam.

  In various embodiments, the ultrasonic surgical instrument can be delivered to the surgeon with the waveguide and / or end effector already operably coupled to the transducer of the surgical instrument. In at least one such embodiment, the surgeon, or other clinician, removes the ultrasonic surgical instrument from the sterile package and inserts the ultrasonic instrument into the generator as outlined above for surgical treatment. Ultrasonic instruments can be used inside. Such a system can eliminate the need for a surgeon, or other clinician, to assemble a waveguide and / or end effector to an ultrasonic surgical instrument. After use of the ultrasonic surgical instrument, the surgeon, or other clinician, can place the ultrasonic instrument in a sealable package that can be transported to a sterilization facility. In the sterilization facility, the ultrasonic instrument can be sterilized and any used parts can be discarded and replaced, while reusable parts can be sterilized and reused. The ultrasonic instrument can then be reassembled, tested, placed in a sterile package, and / or sterilized after being placed in the package. Once sterilized, the reprocessed ultrasonic surgical instrument can be used again.

  While various embodiments have been described herein, many modifications and variations may be made to these embodiments. For example, different types of end effectors can be employed. Also, although materials have been disclosed for particular components, other materials can be used. The above description and the following “claims” are intended to cover all such modifications and variations.

  All of the above U.S. patents and U.S. patent applications, and published U.S. patent applications referred to herein are incorporated herein by reference in their entirety, but the incorporated elements are in the existing definitions. To the extent that it does not conflict with other disclosures described in this disclosure. Thus, to the extent necessary, the disclosure expressly set forth herein shall supersede any conflicting matter incorporated herein by reference. Anything referred to herein as incorporated by reference but inconsistent with the current definitions, descriptions, or other disclosures contained herein, or parts thereof, shall be It shall be incorporated only to the extent that there is no conflict with the current disclosure.

Embodiment
(1) an ultrasonic surgical instrument,
A housing;
An ultrasonic transducer assembly rotatably supported in the housing and in communication with an ultrasonic electrical signal source;
A motor in the housing and in communication with a motor drive signal source, the motor coupled to the ultrasonic transducer assembly to apply rotational motion to the ultrasonic transducer assembly;
A horn coupled to the ultrasonic transducer assembly;
A hollow outer sheath coupled to the housing and having a distal tip formed at the top with at least one cutting edge;
A blade coupled to the horn and having a tissue cutting distal end, wherein the blade is rotatably supported within the outer sheath such that the tissue cutting distal end is at least the hollow outer sheath. An ultrasonic surgical instrument comprising a blade biased into cutting engagement with the at least one cutting edge of a distal tip.
2. The ultrasonic surgical instrument of embodiment 1, wherein a proximal portion of the blade is rotatably supported within an inner sheath supported within the housing.
3. The ultrasonic surgical instrument of embodiment 2, wherein the proximal portion of the blade is rotatably supported in a bushing supported in the inner sheath.
4. The embodiment of claim 3, wherein the bushing is coaxially aligned with a central axis defined by the outer sheath and the blade extends through a hole in the bushing that is not coaxially aligned with the central axis. Ultrasonic surgical instrument.
5. The embodiment of claim 2, wherein a distal portion projects outwardly from the inner sheath and the distal portion of the blade is not coaxially aligned with the proximal portion of the blade. Ultrasonic surgical instrument.
The blade of claim 1, wherein the blade extends rotatably through a lumen of the hollow outer sheath, and the distal tissue cutting end of the blade has an outer diameter that is greater than an inner diameter of the lumen. Sonic surgical instrument.
(7) The embodiment wherein the distal tissue cutting end of the blade has a curved blade tip that is rotatably received within a tip cavity formed in the distal tip of the hollow outer sheath. The ultrasonic surgical instrument according to 1.
The ultrasonic surgical instrument according to claim 7, further comprising a predetermined amount of gap between the curved blade tip and the distal tip of the hollow sheath.
(9) The ultrasonic surgical instrument according to embodiment 1, further comprising a suction port in the outer sheath, wherein suction is applied to the outer sheath from a suction source connected to the suction port.
(10) an ultrasonic surgical instrument,
A housing;
An ultrasonic transducer assembly rotatably supported in the housing and in communication with an ultrasonic electrical signal source;
A motor in the housing and in communication with a motor drive signal source, the motor coupled to the ultrasonic transducer assembly to apply rotational motion to the ultrasonic transducer assembly; ,
A horn coupled to the ultrasonic transducer assembly;
A hollow outer sheath having a distal tip coupled to the housing and defining a tip cavity therein;
A blade coupled to the horn and having a tissue cutting distal end, wherein the blade is rotatably supported in the outer sheath and rotatably supported in the tip cavity. Having a blade; and
An ultrasonic surgical instrument comprising a friction reducing material in the tip cavity.

(11) The ultrasonic surgical instrument according to embodiment 10, wherein the friction reducing material is applied to an inner wall portion of the tip cavity.
12. The ultrasonic surgical instrument of embodiment 10, wherein the friction reducing material comprises a friction reducing pad attached within the tip cavity.
13. The ultrasonic surgical instrument of embodiment 12, wherein the friction reducing pad has a surface that has a surface that conforms to a geometry of a portion of the tissue cutting distal end of the blade member.
(14) The ultrasonic surgical instrument of embodiment 12, wherein the friction reducing pad is made from a material selected from the group consisting of a polyimide material, a Teflon material, a carbon-filled polyimide material, and a Teflon ceramic material.
15. The ultrasonic surgical instrument according to embodiment 10, further comprising another friction reducing material on at least a portion of the tissue cutting distal end of the blade.
(16) an ultrasonic surgical instrument,
A housing;
An ultrasonic transducer assembly rotatably supported in the housing and in communication with an ultrasonic electrical signal source;
A motor in the housing and in communication with a motor drive signal source, the motor coupled to the ultrasonic transducer assembly to apply rotational motion to the ultrasonic transducer assembly; ,
A horn coupled to the ultrasonic transducer assembly;
A hollow outer sheath having a distal tip coupled to the housing and defining a tip cavity therein;
A blade coupled to the horn and rotatably supported in the outer sheath, the blade having a tissue cutting distal end rotatably supported in the tip cavity;
An ultrasonic surgical instrument comprising: a low friction material of at least a portion of the tissue cutting distal end of the blade.
(17) The ultrasonic surgical instrument according to embodiment 16, wherein the low friction material is selected from the group of hard low friction materials consisting of titanium nitride, diamond coating material, chromium nitride, graphite iC (Graphit-iC). .
(18) The tissue cutting distal end of the blade includes a pair of arcuate cutting surfaces separated by a central portion, each arcuate cutting surface having at least one cutting edge formed therein. Embodiment 17. The ultrasonic surgical instrument of embodiment 16, wherein the low friction material is applied to at least a portion of each arcuate cut surface.

Claims (18)

An ultrasonic surgical instrument,
A housing;
An ultrasonic transducer assembly rotatably supported in the housing and in communication with an ultrasonic electrical signal source;
A motor in the housing and in communication with a motor drive signal source, the motor coupled to the ultrasonic transducer assembly to apply rotational motion to the ultrasonic transducer assembly;
A horn coupled to the ultrasonic transducer assembly;
A hollow outer sheath coupled to the housing and having a distal tip formed at the top with at least one cutting edge;
A blade coupled to the horn and having a tissue cutting distal end, wherein the blade is rotatably supported within the outer sheath such that the tissue cutting distal end is at least the hollow outer sheath. An ultrasonic surgical instrument comprising a blade biased into cutting engagement with the at least one cutting edge of a distal tip.   The ultrasonic surgical instrument of claim 1, wherein a proximal portion of the blade is rotatably supported within an inner sheath supported within the housing.   The ultrasonic surgical instrument of claim 2, wherein the proximal portion of the blade is rotatably supported within a bushing supported within the inner sheath.   The ultrasound of claim 3, wherein the bushing is coaxially aligned with a central axis defined by the outer sheath and the blade extends through a hole in the bushing that is not coaxially aligned with the central axis. Surgical instruments.   The ultrasonic surgery of claim 2, wherein a distal portion projects distally out of the inner sheath and the distal portion of the blade is not coaxially aligned with the proximal portion of the blade. Appliances.   The ultrasonic surgical of claim 1, wherein the blade extends rotatably through a lumen of the hollow outer sheath and the distal tissue cutting end of the blade has an outer diameter that is larger than an inner diameter of the lumen. Instruments.   The distal tissue cutting end of the blade has a curved blade tip that is rotatably received within a tip cavity formed in the distal tip of the hollow outer sheath. Ultrasonic surgical instrument.   The ultrasonic surgical instrument according to claim 7, further comprising a predetermined amount of clearance between the curved blade tip and the distal tip of the hollow sheath.   The ultrasonic surgical instrument according to claim 1, further comprising a suction port in the outer sheath, wherein suction is applied to the outer sheath from a suction source coupled to the suction port. An ultrasonic surgical instrument,
A housing;
An ultrasonic transducer assembly rotatably supported in the housing and in communication with an ultrasonic electrical signal source;
A motor in the housing and in communication with a motor drive signal source, the motor coupled to the ultrasonic transducer assembly to apply rotational motion to the ultrasonic transducer assembly; ,
A horn coupled to the ultrasonic transducer assembly;
A hollow outer sheath having a distal tip coupled to the housing and defining a tip cavity therein;
A blade coupled to the horn and having a tissue cutting distal end, wherein the blade is rotatably supported in the outer sheath and rotatably supported in the tip cavity. Having a blade; and
An ultrasonic surgical instrument comprising a friction reducing material in the tip cavity.   The ultrasonic surgical instrument of claim 10, wherein the friction reducing material is applied to an inner wall of the tip cavity.   The ultrasonic surgical instrument according to claim 10, wherein the friction reducing material comprises a friction reducing pad mounted in the tip cavity.   The ultrasonic surgical instrument of claim 12, wherein the friction reducing pad has a surface having a surface that conforms to a geometry of a portion of the tissue cutting distal end of the blade member.   13. The ultrasonic surgical instrument of claim 12, wherein the friction reducing pad is made from a material selected from the group of materials consisting of polyimide material, Teflon material, carbon filled polyimide material, and Teflon ceramic material.   The ultrasonic surgical instrument according to claim 10, further comprising another friction reducing material on at least a portion of the tissue cutting distal end of the blade. An ultrasonic surgical instrument,
A housing;
An ultrasonic transducer assembly rotatably supported in the housing and in communication with an ultrasonic electrical signal source;
A motor in the housing and in communication with a motor drive signal source, the motor coupled to the ultrasonic transducer assembly to apply rotational motion to the ultrasonic transducer assembly; ,
A horn coupled to the ultrasonic transducer assembly;
A hollow outer sheath having a distal tip coupled to the housing and defining a tip cavity therein;
A blade coupled to the horn and rotatably supported in the outer sheath, the blade having a tissue cutting distal end rotatably supported in the tip cavity;
An ultrasonic surgical instrument comprising: a low friction material of at least a portion of the tissue cutting distal end of the blade.   17. The ultrasonic surgical instrument of claim 16, wherein the low friction material is selected from the group of hard low friction materials consisting of titanium nitride, diamond coating material, chromium nitride, graphite iC.   The tissue cutting distal end of the blade includes a pair of arcuate cutting surfaces separated by a central portion, each arcuate cutting surface having at least one cutting edge formed therein; The ultrasonic surgical instrument according to claim 16, wherein a low friction material is applied to at least a portion of each arcuate cutting surface.

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